Stimuli-responsive nanoparticles for biomedical applications

ABSTRACT

Stimuli-responsive NPs with excellent stability, high loading efficiency, encapsulation of multiple agents, targeting to certain cells, tissues or organs of the body, can be used as delivery tools. These NPs contain a hydrophobic inner core and hydrophilic outer shell, which endows them with high stability and the ability to load therapeutic agents with high encapsulation efficiency. The NPs are preferably formed from amphiphilic stimulus-responsive polymers or a mixture of amphiphilic and hydrophobic polymers or compounds, at least one type of which is stimuli-responsive. These NPs can be made so that their cargo is released primarily within target certain cells, tissues or organs of the body, upon exposure to endogenous or exogenous stimuli. The rate of release can be controlled so that it may be a burst, sustained, delayed, or a combination thereof. The NPs have utility as research tools or for clinical applications including diagnostics, therapeutics, or combination of both.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims benefit of and priority to U.S. ProvisionalApplication No. 62/317,033, filed Apr. 1, 2016, which is herebyincorporated herein by reference in its entirety.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

This invention was supported by the National Institutes of Health grantsEB015419 (O.C.F), CA151884 (O.C.F.), HL127464 (O.C.F.), R00CA160350(J.S.) and CA200900 (J.S.).

FIELD OF THE INVENTION

This invention is generally in the field of developingstimuli-responsive solid polymeric nanoparticles (NPs) which can be usedto deliver therapeutic and diagnostic agents including nucleic acids,proteins, chemotherapeutic drugs, or other small molecules.

BACKGROUND OF THE INVENTION

Nanoparticles have become an important tool in many industries includinghealthcare. Biomedical application of NPs has introduced excitingopportunities for the improvement of disease diagnosis and treatment. Inparticular, stimuli-responsive NPs, which can undergo shape, structureand property change upon to endogenous or exogenous stimuli, play anincreasingly important role in a diverse range of biomedicalapplications, such as controlled release of drugs, gene delivery anddiagnostics. The stimuli-responsive characteristic may offerspatiotemporal control over the macroscopic properties of NPs, and thusthe release of the encapsulated cargo can be performed directly at thedesired site, minimizing toxic and side effects in surrounding, healthytissue.

For example, the microenvironment in tumor tissue is different from thenormal tissues. Compared to normal tissues, the pH in tumor tissue ismore acidic, the tissue temperature is relatively higher, and somespecific enzymes or chemicals are over-expressed. Therefore, developingstimuli-responsive NPs that can specifically respond to tumormicroenvironment will accomplish the targeted delivery of cargos totumor sites and thus and impair the toxic and side effects to healthytissues.

The problem with the stimuli responsive NPs is that they often to notmake it to area where release is desired, being phagocytozed, undergoingenzymatic attack, or becoming physically entrapped on their way to thedesired target.

It is therefore an object of the present invention to providestimuli-responsive nanoparticles (NPs) which can be used to delivertherapeutic and diagnostic agents including nucleic acids, proteins,chemotherapeutic drugs, or other small molecules, which have anincreased efficacy in getting to the targeted tissue where release is tooccur.

SUMMARY OF THE INVENTION

Stimuli-responsive NPs with excellent stability, high loadingefficiency, encapsulation of multiple agents, targeting to specificcells, tissues or organs of the body, can be used as delivery tools.These NPs contain a hydrophobic inner core and hydrophilic outer shell,which endows them with high stability in water, aqueous buffers, serumand other biological fluids, or the circulatory system in vivo, and theability to load therapeutic agents with high encapsulation efficiency.The diameters of the nanoparticles are between about 50 nm and about 500nm, preferably between about 50 nm and about 350 nm. In someembodiments, the diameters of the nanoparticles are about 100 nm. Thezeta potential of the nanoparticles are between about −50 mV and about+50 mV, preferably between about −25 mV and +25 mV, most preferablybetween about −10 mV and about +10 my.

Nanoparticles formed from polymers in combination with stimuliresponsive polymers, wherein the stimuli are selected from the groupconsisting of pH, temperature, light, redox change, over-expressedenzymes, hypoxia, sound, magnetic force, electrical energy, andcombinations thereof, are described. Typically, the nanoparticles areformed by emulsion with a non-aqueous solvent, solvent extraction,nanoprecipitation, or a combination thereof.

Preferably, the nanoparticles are formed by self-assembly in an emulsionof a non-aqueous solution with an aqueous solution of a firstamphiphilic polymer containing a polymer represented by Formula I:

(X)_(m)—(Y)_(n)   Formula I

wherein m and n are independently integers between one and 1000,inclusive, X is a hydrophobic polymer and Y is a hydrophilic polymer,and at least one of X, Y, or both, is stimuli-responsive.

In some embodiments, the nanoparticles are formed by self-assembly of amixture of polymers represented by Formula I and a second polymercontaining a polymer represented by Formula II:

(Q)_(c)-(R)_(d)   Formula II

wherein c and d are independently integers between zero and 1000,inclusive, with the proviso that the sum (c+d) is greater than one. Qand R are independently hydrophilic or hydrophobic polymers. Optionally,the nanoparticles are formed by self-assembly of a mixture of polymersrepresented by Formula I and Formula II, wherein the polymer representedby Formula I, Formula II, or both, contains a ligand, wherein the ligandis a targeting ligand, an adhesion ligand, a cell-penetrating ligand,and/or an endosomal-penetrating ligand. Preferably, the ligand isconjugated to the hydrophilic polymer.

In some embodiments, the nanoparticles are formed by self-assembly of amixture of a stimuli-responsive hydrophobic polymer and, optionally afurther polymer containing a polymer represented by Formula III:

(S)_(e)-(T)_(f)   Formula III

wherein e and f are independently integers between one and 1000,inclusive, S is a hydrophilic polymer and T is a hydrophobic polymer. Insome embodiments, the stimuli-responsive hydrophobic polymer, and/or thepolymer represented by Formula III, contains a ligand, wherein theligand is a targeting ligand, an adhesion ligand, a cell-penetratingligand, or an endosomal-penetrating ligand.

The molecular weights of the polymers are between about 1 kDa and about100 kDa, preferably between about 2 kDa and about 50 kDa. In someembodiments, the molecular weights of the polymers are about 2 kDa, 3kDa, 10 kDa, 20 kDa, 30 kDa, or 00 kDa. In embodiments in which thepolymer is amphiphilic, the amphiphilic polymer contains between about5% and about 90% weight/weight of the hydrophobic polymer, preferablybetween about 10% and about 80% weight/weight of the hydrophobicpolymer.

Optionally, the polymers that form the nanoparticles contain linkersbetween the blocks of hydrophilic and hydrophobic polymers, between thehydrophilic polymer and ligand, or both.

These stimuli-responsive NPs have two main components: 1) a hydrophobiccore that is made with stimuli-responsive hydrophobic polymers or thehydrophobic end of amphiphilic polymers to encapsulate therapeutic anddiagnostic agents including proteins or peptides, nucleic acids, lipids,sugars or polysaccharides, small molecules, or combinations thereof; and2) a hydrophilic outer shell that allows the NPs to evade recognition byimmune system components and increase blood circulation half-life.Hydrophobic polymers making up the hydrophobic core can be modified toaccommodate the active agent to be encapsulated. In some embodiments,hydrophobic polymers, or hydrophobic segments of amphiphilic polymers,are modified with charged groups to allow loading of charged activeagents in the hydrophobic core. For example, conjugating a hydrophobiccomponent of a polymer with tetraethylenepentamine or 2-aminoethylmethacrylate will impart a positive charge to the hydrophobic core tohelp encapsulate negatively charged molecules such as nucleic acids.

The stimuli-responsive polymers are hydrophobic or amphiphilic, and canbe, but are not limited to, pH-, hypoxia-, redox-, light-, temperature-,enzyme-, or ultrasound-responsive polymers. The NPs may also include aone or more additional components: 3) a targeting ligand that canspecifically bind to its receptor on certain cells, tissues, or organsof the body; endosomal or cell penetrating molecule; or adhesion ligand.

The stimuli-responsive NPs are made by self-assembly in emulsions of anaqueous solution with a non-aqueous solution, resulting in a polymericnanoparticle that may contain non-aqueous solvent residue. Theamphiphilic copolymers are preferably polyethylene glycol (PEG) basedcopolymers. In a preferred embodiment, the NPs are prepared using amixture of hydrophobic polymer and amphiphilic compound. The amphiphiliccompound can include naturally derived lipids, lipid-like materials,surfactants, or synthesized amphiphilic compounds.

The NPs are useful for delivery of therapeutic, prophylactic, and/ordiagnostic agents. In some embodiments, the NPs contain between about 1%and about 70% weight/weight of a therapeutic agent, a prophylacticagent, a diagnostic agent, or combinations thereof. Preferably, the NPscontain between about 5% and about 50% weight/weight, most preferablybetween about 10% and about 30% weight/weight of a therapeutic agent, aprophylactic agent, a diagnostic agent, or combinations thereof. TheseNPs can be made so that their cargo is released primarily within targetcertain cells, tissues or organs of the body, upon exposure toendogenous or exogenous stimuli (pH, temperature, redox, light, etc.).The rate of release can be controlled so that it may be a burst,sustained, delayed, or a combination thereof. The NPs have utility asresearch tools or for clinical applications including diagnostics,therapeutics, or combination of both.

One specific use of these stimuli-responsive NPs is in the field ofsmall interference RNA (siRNA) delivery. RNA interference (RNAi)technology has gained broad interest among academic and industryinvestigators for its potential to treat a myriad of diseases. One majorhurdle in clinical translation of RNAi therapeutics (e.g., siRNA) may beattributed to the lack of effective and non-toxic delivery vehicles totransport siRNA into diseased tissues and cells. Due to its polyanionicand macromolecular characteristics, naked siRNA cannot freely crosscellular membrane, and thus requires delivery vehicles to facilitate itsintracellular uptake and endosomal escape, as well as to protect it fromdegradation during circulation. Specifically for cancer therapy, thebarriers to effective in vivo siRNA delivery mainly include targeting totumor, penetrating tumor tissue and cell membrane, escaping the endosomeand releasing siRNAs in the cytoplasm. The stimuli-responsive NPs canrespond to tumor or intracellular microenvironment, and thus improve thesiRNA ability to target tumor tissue, escape from endosomes/lysosomes orefficiently release in cytoplasm for high-performance gene silencing.

Besides the delivery of siRNA, the stimuli-responsive NPs can be appliedto the delivery of chemotherapeutic drugs or proteins for cancertherapy. The key principle of cancer therapy is to improve thetherapeutic efficacy and impair the toxic and side effects. Owing totheir scale and distinct physicochemical properties as well as thespecific pathophysiological characteristics of tumors, NPs offer thepotential to significantly improve cancer therapy. However, lack ofactive targeting to cancer cells and the undesired drug release inhealthy tissue are the main barriers to clinical translation. Thedisclosed NPs that are selectively responsive to endogenous or exogenousstimuli offer spatiotemporal control of the delivery of anticancertherapeutics. Moreover, through surface-modification of these NPs bytargeting ligand, it can accomplish the objective that targeted deliveryof chemotherapeutic drugs or proteins to tumor tissues and then rapiddrug release induced by the tumor microenvironment, which thus canminimize toxic and side effects to surrounding healthy tissue.

The delivery of imaging and/or therapeutic agents is an alternative useof the stimuli-responsive NPs for disease diagnostics or theranostic.The microenvironment of diseases is different from the normal tissues.For example, compared to normal tissues, the pH in tumor tissue is moreacidic, the tissue temperature is relatively higher, and some specificenzymes or chemicals are over-expressed. Therefore, developingstimuli-responsive NPs that can specifically respond to tumormicroenvironment will accomplish the site-specific and rapid release ofimaging and/or therapeutic agents at tumor tissue for cancer diagnosticsor theranostic.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-1C are schematic illustrations of (1A) molecular structures ofthe ultra pH-responsive polymer, Meo-PEG-b-P(DPA-co-GMA-TEPA-C14), andthe tumor-penetrating peptide-conjugated polymer, iRGD-PEG-b-PDPA; (1B)ultra pH-responsive and tumor-penetrating nanoplatform for siRNA loadingand release; and (1C) the nanoplatform for targeted in vivo siRNAdelivery and cancer therapy.

FIGS. 2A-2B are graphs showing pH-dependent release from NPs of PDPA80.(2A) Normalized fluorescence intensity as a function of pH for theCy.5.5-labelled NPs of PDPA80. (2B) In vitro siRNA release from the NPsof PDPA80 at 37° C. from pH 7.4 and pH 6.0.

FIGS. 3A-3D are (3A) Luciferase expression in Luc-HeLa cells transfectedwith siRNA-loaded NPs at a 10 nM siRNA dose. (3B) Flow cytometry profileof Luc-HeLa cells incubated with the siRNA-loaded NPs80 and iRGD-NPs80for 4 h. (3C) A histogram showing relative survivin expressiondetermined by Western blot analysis in PC3 cells treated by survivinsiRNA-loaded NPs80 or survivin siRNA-loaded iRGD-NPs80. (3D) A graphshowing proliferation of PC3 cells incubated with survivin siRNA-loadedNPs80 and iRGD-NPs80 at a 10 nM siRNA dose. GL3 siRNA-loaded NPs80 wereused as a control.

FIG. 4 is a bar graph showing cell viability of Luc-HeLa cells in thepresence of 10 nM siRNA dose of the GL3 siRNA-loaded NPs and Lipo2K-GL3siRNA complex. Blank: cells incubated with free medium.

FIGS. 5A-5D are graphs showing relative fluorescence intensity ofintegrins αvβ3 and αvβ5 on Luc-HeLa (5A, 5C) and PC3 (5B, 5D) cellsdetermined by flow cytometry analysis. Blank: cells incubated with freemedium; MFI-mean fluorescence intensity.

FIGS. 6A-6C are graphs showing relative fluorescence intensity ofDY745-siRNA-loaded NPs80 and iRGD-NPs80. (6A) Flow cytometry profile ofPC3 cells incubated with DY745-siRNA-loaded NPs80 and iRGD-NPs80 for 4 hat a 10 nM siRNA dose. Mean fluorescence intensity (MFI) of Luc-HeLa6(B) and PC3 (6C) cells incubated with DY547-siRNA-loaded NPs80 andiRGD-NPs80 for 4 h at a 10 nM siRNA dose. *p<0.05.

FIGS. 7A-7D are histograms showing firefly luciferase expression inLuc-HeLa cells transfected with GL3 siRNA-loaded NPs of (7A)Meo-PEG113-b-P(DPA80-co-GMA5-TEPA), and (7B)Meo-PEG113-b-P(MMA80-co-GMA5-TEPA-C14) at a siRNA dose from 0-50 nM; andcytotoxicity of GL3 siRNA-loaded NPs of (7C)Meo-PEG113-b-P(DPA80-co-GMA5-TEPA) and (7D)Meo-PEG113-b-P(MMA80-co-GMA5-TEPA-C14) against Luc-HeLa cells at a siRNAdose 0-50 nM.

FIGS. 8A-8B are graphs showing (8A) pharmacokinetics of naked siRNA, andsiRNA-loaded NPs; (8B) biodistribution of the NPs in the PC3 xenografttumor-bearing mice sacrificed at 24 h post-injection of naked siRNA, andsiRNA-loaded NPs.

FIG. 9 is a bar graph showing survivin expression in PC3 xenograft tumorof the mice treated by GL3 siRNA-loaded NPs80 (Control NPs), andsurvivin siRNA-loaded NPs80 and iRGD-NPs80.

FIG. 10 is a graph showing relative tumor size over time (days) of thePC3 xenograft tumor-bearing mice after treatment by PBS, control NPs,and survivin siRNA-loaded NPs. The intravenous injections are indicatedby the arrows. * P<0.05; ** P<0.01.

FIG. 11 is graph showing body weight over time (days) of the PC3xenograft tumor-bearing nude mice treated with PBS, GL3 siRNA-loadedNPs80 (Control NPs), and survivin siRNA-loaded NPs80 and iRGD-NPs80.

FIGS. 12A-12C are schematic illustrations of (12A) molecular structuresof the oligoarginine-functionalized ultra pH-responsive polymer,Meo-PEG-b-P(DPA-co-GMA-Rn), and PCa-specific polymer, ACUPA-PEG-b-PDPA;(12B) endosomal membrane-penetrating and ultra pH-responsivenanoplatform for siRNA loading and release; and (12C) the nanoplatformfor in vivo PCa-specific siRNA delivery and cancer therapy.

FIGS. 13A-13D are graphs showing (13A) size and polydispersity (PDI) ofthe GL3 siRNA-loaded NPs of Meo-PEG-b-P(DPA-co-GMA-Rn) as a function ofnumber of arginine residues; (13B) Zeta potential (ζ) and encapsulationefficiency (EE %) of the GL3 siRNA-loaded NPs ofMeo-PEG-b-P(DPA-co-GMA-Rn) as a function of number of arginine residues;(13C) acid-base titration profile of Meo-PEG-b-P(DPA-co-GMA-R10) atincreasing NaOH concentrations. (13D) In vitro release of DY745-siRNAover time (hours) from the NPs of Meo-PEG-b-P(DPA-co-GMA-R10) at a pH of6.0 and 7.4.

FIG. 14 is a graph showing normalized fluorescence intensity as afunction of pH for the Cy.5.5 labelled NPs ofMeo-PEG-b-P(DPA-co-GMA-R10).

FIGS. 15A-15C are graphs showing (15A) firefly luciferase expression inLuc-HeLa cells transfected with GL3 siRNA-loaded NPs ofMeo-PEG-b-P(DPA-co-GMA-Rn) and Lipo2K-siRNA complex at a 10 nM siRNAdose; (15B) flow cytometry profile of Luc-HeLa cells incubated with theDY547-siRNA-loaded NPsR10 and ACUPA-NPsR10 for 4 h; and (15C) a graphshowing proliferation over time (days) of LNCaP cells treated with PHB1siRNA-loaded NPsR10 and ACUPA-NPsR10 at a 10 nM siRNA dose. GL3siRNA-loaded NPsR10 were used as a control.

FIGS. 16A-16F are graphs showing flow cytometry profiles of PSMA onLuc-HeLa (16A) and PCa cells including PC3 (16B), DU145 (16C), 22RV1(16D), and LNCaP (16E) determined by flow cytometry analysis. (16F) is asummary bar graph showing the fluorescence intensity of PSMA inLuc-HeLa, PC3, DU145, 22RV1, and LNCaP cells. Blank: cells incubatedwith free medium; MFI-mean fluorescence intensity.

FIGS. 17A-17F are flow cytometry profiles and mean fluorescenceintensity (MFI) of Luc-HeLa (17A, 17D), PC3 (17B, 17E) and DU145 (17C,17F) cells incubated with DY546-siRNA loaded NPsR10 and ACUPA-NPsR10 for4 h at a 10 nM siRNA dose. Blank: cells incubated with free medium.

FIG. 17 is a bar graph showing cytotoxicity of the GL2 siRNA loaded NPsand Lipo1K-GL3 siRNA complex against Luc-HeLa cells at a 10 nM siRNAdose. Control: cells incubated with free medium.

FIGS. 19A-19B are bar graphs showing (19A) firefly luciferase expressionin Luc-HeLa cells transfected with GL3 siRNA-loaded NPs and ACUPA-NPs ofMeo-PEG-b-P(DPA-co-GMA-TEPA) at a siRNA dose from 0-50 nM; (19B)cytotoxicity of GL3 siRNA-loaded NPs and ACUPA-NPs ofMeo-PEG-b-P(DPA-co-GMA-TEPA) against Luc-HeLa cells at a siRNA dose of0-50 nM.

FIG. 20 is a bar graph showing Mean fluorescence intensity (MFI)determined by the flow cytometry profiles of LNCaP cells incubated withDY547-siRNA-loaded NPsR10 and ACUPA-NPsR10 for 4 h, and anti-PSMA for 30min followed by ACUPA-NPsR10 for another 4 h at a 10 nM siRNA dose.Blank: cells incubated with free medium. * P<0.5

FIG. 21 is a bar graph showing relative expression of PHB1 determined byWestern blot analysis in LNCaP cells treated with PHB1 siRNA-loadedNPsR10 and ACUPA-NPsR10. GL3 siRNA-loaded NPsR10 were used as a control.

FIGS. 22A-22B are graphs showing (22A) pharmacokinetics over time(hours) of naked DY647-siRNA, and DY647-siRNA-loaded NPsR10 andACUPA-NPsR10; (22B) biodistribution of the NPs in the tumors and mainorgans of the LNCaP xenograft tumor-bearing nude mice sacrificed 24 hpost-injection of naked Cy5.5-siRNA, Cy5.5-siRNA-loaded NPsR10 andACUPA-NPsR10, and PSMA antibody followed by Cy5.5-siRNA-loadedACUPA-NPsR10.

FIG. 23 is a graph showing relative tumor size over time (days) of theLNCaP xenograft tumor-bearing nude mice after treatment by PBS, controlNPs, and PHB1 siRNA-loaded NPsR10 and ACUPA-NPsR10. The intravenousinjections are indicated by the arrows. GL3 siRNA-loaded NPsR10 wereused as a control. * P<0.05; ** P<0.01 FIG. 24 is a bar graph showingPHB1 expression in LNCaP xenograft tumor of the mice treated with GL3siRNA-loaded NPsR10 (Control NPs), and PHB1 siRNA-loaded NPsR10 andACUPA-NPsR10.

FIG. 25 is a graph showing body weight of the LNCaP xenografttumor-bearing nude mice treated with PBS, GL3 siRNA loaded NPsR10(Control NPs), and PHB1 siRNA-loaded NPsR10 and ACUPA-NPsR10.

FIGS. 26A-26B are schematics of (26A) molecular structure of Cy5.5conjugated ultra pH-responsive copolymer,Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5; (26B) the self-assembly ofMeo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5) into nanoparticles with theaggregation of Cy5.5 inside the hydrophobic cores.

FIGS. 27A and 27B are (27A) a molecular structure of ultra pH-responsivepolymer, Meo-PEG-b-PDPA and (27B) a graph showing cumulative releaseprofile of PTX from the PTX loaded NPs of Meo-PEG-b-PDPA in PBS bufferat a pH of 7.4 and 5.0.

FIGS. 28A-28B are (28A) molecular structure of light-responsive polymer,Meo-PEG-b-POPEMA; and (28B) GPC profiles of the light-responsiveMeo-PEG-b-POPEMA before and after 365 nm UV light irradiation.

FIGS. 29A-29B are (29A) cumulative release profile over time (hours) ofDTX from the DTX loaded NPs of Meo-PEG-b-POPEMA in PBS buffer (7.4); and(29B) cytotoxicity of free DTX and DTX loaded NPs of Meo-PEG-b-POPEMAagainst PC3 cells at increasing concentrations of DTX. After incubationwith the free DTX or DTX loaded NPs for 8 h, the culture medium wasreplaced and UV irradiation was applied for 30 min and then the cellswere further incubated for another 40 h.

FIG. 30 is a schematic illustration of the self-assembly ofredox-responsive polymer into spherical NPs for siRNA delivery andcancer therapy.

FIGS. 31A-31B are graphs showing (31A) size change over time (min) ofthe NPs of PDSA8-1 incubated in PBS buffer containing 10 mM GSH for 4 h;and (31B) firefly luciferase expression in Luc-HeLa cells transfectedwith GL3 siRNA loaded NPs of PDSA polymers at a 1 nM siRNA dose.

FIG. 32 is a graph showing proliferation over time (days) of PC3 cellstreated with KIF11 siRNA loaded NPs of PDSA8-1. GL3 siRNA loaded NPswere used as a control.

FIG. 33 is a graph showing pharmacokinetics over time (hours) of nakedDY647-siRNA, and DY647-siRNA loaded NPs of PDSA8-1.

FIG. 34 is a bar graph showing relative levels of KIF11 expression byWestern blot analysis in the PC3 tumor tissue after systemic treatmentby KIF11 siRNA loaded NPs of PDSA8-1. GL3 siRNA loaded NPs were used asa control.

FIG. 35 is a graph showing relative tumor size over time (days) of thePC3 xenograft tumor-bearing nude mice after treatment by PBS, controlNPs, naked KIF11 siRNA and KIF11 siRNA loaded NPs of PDSA8-1. Theintravenous injections are indicated by the arrows. GL3 siRNA loaded NPswere used as a control.

FIG. 36 is molecular structure of ultra pH-responsive polymer, PDPA; agraph showing cumulative release profile of PTX from the PTX loaded NPsof PDPA in PBS buffer at a pH of 7.4 and 5.0.

FIG. 37 a schematic illustration of illustration of the TMEpH-responsive multistaged nanoplatform for systemic siRNA delivery andeffective cancer therapy. After intravenous injection (i), the siRNAloaded NPs can first extravasate from leaky tumor vasculature andaccumulate in the tumor tissue (ii). Subsequently, the NPs respond toTME pH to fast release siRNA/TCPA complexes (iii), which then target andpenetrate tumor cells (iv) to eventually achieve efficient cytosolicsiRNA delivery and gene silencing (v).

FIGS. 38A-38B are (38A) a graph showing emission fluorescence spectrumof Cy5.5-labelled TME pH-responsive NPs at different pHs. Ex=675 nm;(38B) a graph showing cumulative siRNA release from the DY-677 siRNAloaded TCPA2-NPs at pH 7.4 and pH 6.8.

FIG. 39 is a graph showing fluorescent emission spectra of naked LucsiRNA, and Luc siRNA loaded TCPA2-NPs incubated with RNase for 5 min, 10min, 15 min, and 6 hr. Fluorescein was labelled at 5′-end of the sensestrand and its quencher Dabcyl was labeled at the 3′-end of theantisense strand.

FIGS. 40A-40C are (40A) a plot showing count rate of the siRNA loadedTCPA2-NPs incubated in PBS buffer (pH 6.8) over a period of 10 min.;(40B) a bar graph showing size distribution of TCPA2-NPs incubated inPBS buffer at pH 6.8; (40C) a plot showing cumulative siRNA release fromthe DY-677 siRNA loaded TCPA2-NPs at pH 7.4, and pH 6.8.

FIGS. 41A-41D are (41A) a graph showing flow cytometry profile, and(41B) a bar graph showing MFI of Luc-HeLa cells incubated withDY677-siRNA loaded TCPA2-NPs at pH 7.4, and pH 6.8 for 2 hr. (41C) Lucexpression in Luc-HeLa cells treated with Luc siRNA loaded TCPA2-NPs atpH 7.4, and pH 6.8; (41D) a bar graph showing viability of Luc-HeLacells treated with Luc siRNA loaded TCPA2-NPs at different siRNA doses.

FIGS. 42A-42C are (FIG. 42A) a bar graph quantifying Western blotanalysis of BRD4 expression in LNCaP cells treated with BRD4 siRNAloaded TCPA2-NPs at pH 7.4, and pH 6.8; (FIG. 42B) a bar graphsummarizing flow cytometry analysis of apoptosis of LNCaP cells treatedwith BRD4 siRNA loaded TCPA2-NPs at a 20 nM siRNA dose at pH 7.4, and pH6.8; (FIG. 42C) a plot showing proliferation profile of LNCaP cellstreated with BRD4 siRNA loaded TCPA2-NPs at a 20 nM siRNA dose at pH7.4, and pH 6.8. Luc siRNA loaded TCPA2-NPs were used as control.

FIGS. 43A-43B are a plot (FIG. 43A) showing pharmacokinetics of nakedDY677-siRNA and siRNA loaded TCPA2-NPs; and a bar graph (FIG. 43B)showing biodistribution of the NPs quantified from fluorescent images ofthe tumors and main organs of LNCaP xenograft tumor-bearing nude micesacrificed 24 h post injection of naked DY677-siRNA and siRNA loadedTCPA2-NPs.

FIGS. 44A-44B are graphs showing relative tumor size (44A) and tumorweight (44B) of the LNCaP xenograft tumor-bearing nude mice (n=5) aftersystemic treatment by PBS, naked BRD4 siRNA, control NPs, and BRD4 siRNAloaded TCPA2-NPs, where intravenous injections are indicated by thearrows. Luc siRNA loaded TCPA2-NPs were used as control NPs.

DETAILED DESCRIPTION OF THE INVENTION I. Definitions

“Binding,” as used herein, refers to the interaction between acorresponding pair of molecules or portions thereof that exhibit mutualaffinity or binding capacity, typically due to specific or non-specificbinding or interaction, including, but not limited to, biochemical,physiological, and/or chemical interactions.

“Binding partner” as used herein refers to a molecule that can undergobinding with a particular molecule.

“Biological binding” defines a type of interaction that occurs betweenpairs of molecules including proteins, peptides, nucleic acids,glycoproteins, carbohydrates, or endogenous small molecules.

“Specific binding” as used herein refers to molecules, such aspolynucleotides, that are able to bind to or recognize a binding partner(or a limited number of binding partners) to a substantially higherdegree than to other, similar biological entities.

A “biocompatible polymer” is used here to refer to a polymer that doesnot typically induce an adverse response when inserted or injected intoa living subject, for example, without significant inflammation and/oracute rejection of the polymer by the immune system, for instance, via aT-cell response.

A “copolymer” herein refers to more than one type of repeat unit presentwithin the polymer defined below.

“Encapsulation efficiency” (EE) as used herein is the fraction ofinitial drug that is encapsulated by the nanoparticles (NPs).

“loading” as used herein refers to the mass fraction of encapsulatedagent in the NPs.

A “polymer,” as used herein, is given its ordinary meaning as used inthe art, i.e., a molecular structure including one or more repeat units(monomers), connected by covalent bonds. The polymer may be a copolymer.The repeat units forming the copolymer may be arranged in any fashion.For example, the repeat units may be arranged in a random order, in analternating order, or as a “block” copolymer, i.e., including one ormore regions each including a first repeat unit (e.g., a first block),and one or more regions each including a second repeat unit (e.g., asecond block), etc. Block copolymers may have two (a diblock copolymer),three (a triblock copolymer), or more numbers of distinct blocks.

A “polymeric conjugate” as used herein refers to two or more polymers(such as those described herein) that have been associated with eachother, usually by covalent bonding of the two or more polymers together.

As used herein, a nanoparticle refers to a polymeric particle that canbe formed using a solvent emulsion, spray drying, or precipitation inbulk or microfluids, wherein the solvent is removed to no more than aninsignificant residue, leaving a solid (which may, or may not, be hollowor have a liquid filled interior) polymeric particle, unlike a micellewhose form is dependent upon being present in an aqueous solution.

As used herein, the term “carrier” or “excipient” refers to an organicor inorganic ingredient, natural or synthetic inactive ingredient in aformulation, with which one or more active ingredients are combined.

As used herein, the term “pharmaceutically acceptable” means a non-toxicmaterial that does not interfere with the effectiveness of thebiological activity of the active ingredients.

As used herein, the terms “effective amount” or “therapeuticallyeffective amount” means a dosage sufficient to alleviate one or moresymptoms of a disorder, disease, or condition being treated, or tootherwise provide a desired pharmacologic and/or physiologic effect. Theprecise dosage will vary according to a variety of factors such assubject-dependent variables (e.g., age, immune system health, etc.), thedisease or disorder being treated, as well as the route ofadministration and the pharmacokinetics of the agent being administered.

As used herein, the term “prevention” or “preventing” means toadminister a composition to a subject or a system at risk for or havinga predisposition for one or more symptom caused by a disease or disorderto cause cessation of a particular symptom of the disease or disorder, areduction or prevention of one or more symptoms of the disease ordisorder, a reduction in the severity of the disease or disorder, thecomplete ablation of the disease or disorder, stabilization or delay ofthe development or progression of the disease or disorder.

The terms “bioactive agent” and “active agent”, as used interchangeablyherein, include, without limitation, physiologically orpharmacologically active substances that act locally or systemically inthe body. A bioactive agent is a substance used for the treatment (e.g.,therapeutic agent), prevention (e.g., prophylactic agent), diagnosis(e.g., diagnostic agent), cure or mitigation of disease or illness, asubstance which affects the structure or function of the body, orpro-drugs, which become biologically active or more active after theyhave been placed in a predetermined physiological environment.

The terms “sufficient” and “effective”, as used interchangeably herein,refer to an amount (e.g. mass, volume, dosage, concentration, and/ortime period) needed to achieve one or more desired result(s).

The term “protein” “polypeptide” or “peptide” refers to a natural orsynthetic molecule comprising two or more amino acids linked by thecarboxyl group of one amino acid to the alpha amino group of another.

The term “polynucleotide” or “nucleic acid sequence” refers to a naturalor synthetic molecule comprising two or more nucleotides linked by aphosphate group at the 3′ position of one nucleotide to the 5′ end ofanother nucleotide. The polynucleotide is not limited by length, andthus the polynucleotide can include deoxyribonucleic acid (DNA) orribonucleic acid (RNA).

II. Stimuli-responsive Nanoparticles

A long-circulating, optionally cell-penetrating, and stimuli-responsiveNP platform for effective in vivo delivery of therapeutic, prophylacticand/or diagnostic agents is made of an amphiphilic polymer, mostpreferably a PEGylated polymer, which shows a response to a stimulussuch as pH, temperature, or light, such as an ultra pH-responsivecharacteristic with a pKa close to the endosomal pH (6.0-6.5) (Wang Y etal, Nat Mater, 13, 204-212 (2014)). The polymer may include a targeting,cell penetrating, and/or adhesion molecule such as a tumor-targetingpeptide iRGD (FIGS. 1A-1B). In some embodiments, the targeting, cellpenetrating, and/or adhesion molecule are convalently conjugated to oneor more of the polymer. In other embodiments, the targeting, cellpenetrating, and/or adhesion molecule are associated with thenanoparticles formed by one or more polymers via non-covalentassociation.

Generally, the disclosed nanoparticles have prolonged circulation i.e.,increased half-life in the blood compared to controls withoutstimuli-responsive element, PEGylation, targeting moiety, orcombinations thereof. In some embodiments, the disclosed nanoparticleshave a half-life of about, or more than, 3 hours, 4 hours, 5 hours, 6hours, 7 hours, 8 hours, 9 hours, 10 hours, 11 hours, 12 hours, 24hours, at least a day, or more than a day.

Typically, the disclosed nanoparticles have increased accumulation attarget site such as tumor sites compared to controls withoutstimuli-responsive element, PEGylation, targeting moiety, orcombinations thereof. Preferably, the disclosed nanoparticles havedeeper penetration into the tumor tissues compared to controls withoutstimuli-responsive element,

PEGylation, targeting moiety, or combinations thereof. In someembodiments, the disclosed nanoparticles have increased accumulation attarget site by about, or more than, 50%, 100%, 200%, 300%, 400%, or500%.

In preferred embodiments, the disclosed nanoparticles have enhanceduptake by tumor cells compared to controls without stimuli-responsiveelement, PEGylation, targeting moiety, or combinations thereof. In someembodiments, the disclosed nanoparticles have increased uptake by targetcells by about, or more than, 50%, 100%, 200%, 300%, 400%, or 500%. Infurther preferred embodiments, the disclosed nanoparticles have greaterintracellular cargo release without stimuli-responsive element,PEGylation, targeting moiety, or combinations thereof. In someembodiments, the disclosed nanoparticles have increased intracellularcargo release in target cells by about, or more than, 50%, 100%, 200%,300%, 400%, or 500%.

When tumor cells are targeted, the disclosed nanoparticles carryingactive agents targeting tumor cells can suppress tumor growth. In someembodiments, the disclosed nanoparticles can reduce tumor growth by 10%,20%, 30%, 40%, 50%, 60%, 70%, 80%, or 90%. When the active agent issiRNA or shRNA to knowndown a therapeutic target of the tumor cells, thedisclosed nanoparticles can knockdown the particular target by 10%, 20%,30%, 40%, 50%, 60%, 70%, 80%, or 90%.

Generally, stimuli-responsive nanoparticles are prepared using one ormore amphiphilic copolymers through selection of a hydrophilic orhydrophobic polymer component of the copolymer, or by modification ofthe hydrophilic or hydrophobic polymers.

A. Polymers

Typically, the nanoparticles can be formed by self-assembly in anemulsion of a non-aqueous solvent with an aqueous solvent of a firstamphiphilic polymer containing a polymer represented by Formula I:

(X)_(m)—(Y)_(n)   Formula I

wherein, m and n are independently integers between one and 1000,inclusive. X is a hydrophobic polymer and Y is a hydrophilic polymer,and at least one of X, Y, or both, is stimuli-responsive.

In some embodiments, Y is methoxyl-polyethylene glycol (Meo-PEG). In oneembodiment, X is selected from the group consisting of poly(2-(diisopropylamino) ethyl methacrylate (PDPA),poly(2-(hexamethyleneimino) ethyl methacrylate (PHMEMA), L-cystine-basedpoly(disulfide) (PDSA), and poly (2-(2-oxo-2-phenylacetoxy) ethylmethacrylate) (POPEMA). In some embodiments, X is a hydrophobiccopolymer and/or Y is a hydrophilic copolymer. In one embodiment, X ispoly (2-(diisopropylamino) ethylmethacrylate-co-glycidyl methacrylate(P(DPA-co-GMA)). Generally, the hydrophobic polymer X forms thehydrophobic core of the nanoparticle, suitable for encapsulatinghydrophobic active agents within the nanoparticle.

In some embodiments, one or more parts of the hydrophobic polymer X isfurther modified with hydrophilic groups to impart charges such that thehydrophobic core of the nanoparticle contains an inner hydrophilic corefor encapsulating hydrophilic active agents such as nucleic acids.Examplary modifications include including 2-aminoethyl methacrylate(AMA), tetraethylenepentamine (TEPA), TEPA-C14. In one embodiment, X isP(DPA-co-GMA-TEPA), P(DPA-co-GMA-TEPA-C14), or poly(2-(hexamethyleneimino) ethyl methacrylate-co-2-aminoethyl methacrylate)(P(HMEMA-co-AMA)).

In preferred embodiments, the amphiphilic polymer represented by FormulaI is selected from the group consisting of Meo-PEG-b-P(DPA-co-GMA),Meo-PEG-b-P(DPA-co-GMA-TEPA-C14), Meo-PEG-b-P(DPA-co-GMA-Rn),Meo-PEG-b-P(DPA-co-GMA-TEPA), Meo-PEG113-b-PDPA, Meo-PEG-b-PHMEMA,Meo-PEG-b-P(HMEMA-co-AMA), Meo-PEG-b-POPEMA, and combinations thereof.

In some embodiments, the first amphiphilic polymer represented byFormula I contains a ligand, wherein the ligand is a targeting ligand,an adhesion ligand, a cell-penetrating ligand, or anendosomal-penetrating ligand, conjugated to X, Y, or both. In someembodiments, the ligand is oligoarginine (NH₂—R_(n)—CONH₂, where n isany integer between about 6 to about 100, for example n=6, 8, 10, 20, or30) attached to the hydrophobic polyer of Formula I, for example,Meo-PEG-b-P(DPA-co-GMA-R_(n)). In one embodiment, the ligand isNH₂—R₈—CONH₂ (SEQ ID NO:15).

Optionally, the nanoparticles are formed by self-assembly of a mixtureof polymers represented by Formula I, and a second polymer containing apolymer represented by Formula II:

(Q)_(c)-(R)_(d)   Formula II

wherein, c and d are independently integers between zero and 1000,inclusive, with the proviso that the sum (c+d) is greater than one. Qand R are independently hydrophilic or hydrophobic polymers.

In some embodiments, the nanoparticles are formed by self-assembly of amixture of polymers represented by Formula I and Formula II, wherein thepolymer represented by Formula I, Formula II, or both, contains aligand, wherein the ligand is a targeting ligand, an adhesion ligand, acell-penetrating ligand, or an endosomal-penetrating ligand, with theproviso that the ligand is conjugated to the hydrophilic polymer.Examplary ligands include a disulfide-based cyclicarginine-glycine-aspartic acid (RGD) peptide (iRGD), a tumor targetingmoiety S,S-2-[3-[5-amino-1-carboxypentyl]-ureido]-pentanedioic acid(ACUPA), and a fluorescent Cyanine 5.5 (CY5.5®) dye.

In one embodiment, the nanoparticles are formed by self-assembly of amixture of methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate-tetraethylenepentamine-C14)(Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)), and iRGD-PEG-b-PDPA. In anotherembodiment, the nanoparticles are formed by self-assembly of a mixtureof methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate-oligoarginine)(Meo-PEG-b-P(DPA-co-GMA-Rn)), and ACUPA-PEG-b-PDPA.

Besides amphiphilic copolymers, hydrophobic polymers can be also used todevelop stimuli-responsive NPs for various biomedical applications. Inone embodiment, the hydrophobic polymer is poly (2-(diisopropylamino)ethyl methacrylate (PDPA), or derivatives thereof. In anotherembodiment, the hydrophobic polymer is poly (2-(2-oxo-2-phenylacetoxy)ethyl methacrylate) (POPEMA), or derivatives thereof. In a furtherembodiment, the hydrophobic polymer is poly (2-(2-oxo-2-phenylacetoxy)ethyl methacrylate) (POPEMA). Any hydrophobic polymers can be used toprepare amphiphilic polymers by conjugating to one or more hydrophobicpolymers such as polyethylene glycol, or derivatives thereof.

In some embodiments, the nanoparticles are formed by self-assembly of amixture of a stimuli-responsive hydrophobic polymer, and optionally, afurther polymer containing a polymer represented by Formula III:

(S)_(e)-(T)_(f)   Formula III

wherein, e and f are independently integers between zero and 1000,inclusive, with the proviso that the sum (e+f) is greater than one. Sand T are independently a hydrophilic polymer or a hydrophobic polymer.In some embodiments, the stimuli-response hydrophobic polymer, thepolymer represented by Formula III, or both contains a ligand, whereinthe ligand is a targeting ligand, an adhesion ligand, a cell-penetratingligand, and/or an endosomal-penetrating ligand, with the proviso thatthe ligand is conjugated to the hydrophilic polymer.

For hydrophobic polymers, their nanoparticles are generally prepared byusing the mixture of the hydrophobic polymer and amphiphilic polymer oramphiphilic compound. The amphiphilic compound can include, but is notlimited to, one or a plurality of naturally derived lipids, PEG-modifiedlipid, lipid-like materials, surfactants, or synthesized amphiphiliccompounds. In one embodiment, the amphiphilic compound is a lipid-PEGsuch as 1, 2-distearoyl-sn-glycero-3-phosphoethanolamine-poly(ethyleneglycol)-3000 (DSPE-PEG 3000).

In some embodiments, the nanoparticles are formed by self-assembly of amixture of a stimuli-responsive hydrophilic polymer, and optionally, afurther polymer containing a polymer represented by Formula III:

(S)_(e)-(T)_(f)   Formula III

wherein, e and f are independently integers between zero and 1000,inclusive, with the proviso that the sum (e+f) is greater than one. Sand T are independently a hydrophilic polymer or a hydrophobic polymer.Optionally, the first stimuli-response hydrophilic polymer, the polymerrepresented by Formula III, or both contains a ligand, wherein theligand is a targeting ligand, an adhesion ligand, a cell-penetratingligand, or an endosomal-penetrating ligand, with the proviso that theligand is conjugated to the hydrophilic polymer.

Optionally, the polymers that form the nanoparticles contain linkersbetween the blocks of hydrophilic and hydrophobic polymers, between thehydrophilic polymer and ligand, or both.

Amphiphilic copolymers can spontaneously self-assemble in aqueoussolution to form NPs with hydrophobic inner core and hydrophilic outershells. The hydrophobic inner core can be used to deliver therapeutic,and/or diagnostic agents including nucleic acids, proteins,chemotherapeutic drugs, or small molecules. The incorporation ofstimuli-responsive moieties to the hydrophobic core can easilyaccomplish the spatiotemporal control over the macroscopic properties ofNPs, and thereby the release of the encapsulated cargo at the desiredsite.

The amphiphilic polymers are responsive to a stimulus. This may be a pHchange, redox change, temperature change, exposure to light or otherstimuli, including binding to a target, and sensing reduction in oxygenconcentrations (hypoxia). The responsiveness may be imparted solely bythe hydrophilic polymer, the hydrophobic polymer, or the conjugate perse. The nanoparticles are formed of a mixture or blend of polymers. Somemay be the amphiphilic polymers, preferably copolymers of modifiedpolyethylene glycol (PEG) and polyesters, such as various forms ofPLGA-PEG or PLA-PEG copolymers, collectively referred to herein as“PEGylated polymers”, some hydrophobic polymer such as PLGA, PLA or PGA,and/or some may be hydrophilic polymer such as a PEG, or PEG derivative.Some will be modified by conjugation to a targeting agent, a celladhesion or a cell penetrating peptide.

The length of hydrophilic and/or hydrophobic polymers can be optimizedto optimize encapsulation of agent to be delivered, i.e., encapsulationefficiency (EE %). As demonstrated in the examples, as the PDPA lengthincreases, the EE % and size of the resulting NPs increase (Table 3),possibly because the increased PDPA length leads to an increase in thesize of the hydrophobic core. Specifically, the EE % reaches almost 100%for the polymer with 80 (PDPA80) or 100 (PDPA100) DPA repeat units.Notably, using a mixture of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) (90 mol %)and tumor-penetrating polymer (iRGD-PEG-b-PDPA, 10 mol %, FIG. 1A) toprepare NPs does not cause obvious change in the EE % or particle size.

The amphiphilic polymers include a hydrophilic polymer. This ispreferably at an end which can orient to the exterior of thenanoparticles when formed by emulsion techniques such as self-assembly.

Polymers and copolymers that can be used to make the nanoparticlesdisclosed herein include, but are not limited to, polymers includingglycolic acid units, referred to herein as “PGA”, and lactic acid units,such as poly-L-lactic acid, poly-D-Iactic acid, poly-D,L-Iactic acid,poly-L-Iactide, poly-D-Iactide, and poly-D,L-Iactide, collectivelyreferred to herein as “PLA”, and caprolactone units, such aspoly(8-caprolactone), collectively referred to herein as “PCL”; andcopolymers including lactic acid and glycolic acid units, such asvarious forms of poly(lactic acid-co-glycolic acid) andpoly(lactide-co-glycolide) characterized by the ratio of lacticacid:glycolic acid, collectively referred to herein as “PLGA”;polyacrylates, polyanhydrides, poly (ester anhydrides),poly-4-hydroxybutyrate (P4HB) combinations and derivatives thereof.

The polymer is preferably a biocompatible polymer. One simple test todetermine biocompatibility is to expose a polymer to cells in vitro;biocompatible polymers are polymers that typically will not result insignificant cell death at moderate concentrations, e.g., atconcentrations of 50 micrograms/10⁶ cells. For instance, a biocompatiblepolymer may cause less than about 20% cell death when exposed to cellssuch as fibroblasts or epithelial cells, even if phagocytosed orotherwise uptaken by such cells.

The biocompatible polymer is preferably biodegradable, i.e., the polymeris able to degrade, chemically and/or biologically, within aphysiological environment, such as within the body.

Stimuli that the Polymers can be Responsive to

The polymers can be responsive to changes in pH-, redox-, light-,temperature-, enzyme-, ultrasound, or other stimuli such as aconformation change resulting from binding.

Almeida, et al. J. Applied Pharm.l Sci. 02 (06)01-10 (2012) is anexcellent review of stimuli responsive polymers. The signs or stimulithat trigger the structural changes on smart polymers can be classifiedin three main groups: physical stimuli (temperature, ultrasound, light,mechanical stress), chemical stimuli (pH and ionic strength) andbiological stimuli (enzymes and bio molecules).

Stimuli can be artificially controlled (with a magnetic or electricfield, light, ultrasounds, etc.) or naturally promoted by internalphysiological environment through a feedback mechanism, leading tochanges in the polymer net that allow the drug delivery without anyexternal intervention (for example: pH changes in certain vital organsor related to a disease; temperature change or presence of enzymes orother antigens) or by the physiological condition. In the presence of asign or stimuli, changes can happen on the surface and solubility of thepolymer as well as on sol-gel transition.

Smart polymers can be classified according to the stimuli they respondto or to their physical features. Regarding the physical shape, they canbe classified as free linear polymer chain solutions, reversible gelscovalently cross-linked and polymer chain grafted to the surface.

Stimuli responsive polymers are also reviewed by James, et al., ActaPharma. Sinica B 4(2):120-127 (2014). The following is a list ofexemplary polymers categorized by responsive to various stimuli:

Temperature: POLOXAMERS, poly(N-alkylacrylamide)s,poly(N-vinylcaprolactam)s, cellulose, xyoglucan, and chitosan

pH: poly(methacrylic acid)s, poly(vinylpyridine)s, andpoly(vinylimmidazole)s

light: modified poly(acrylamide)s

electric field: sulfonated polystyrenes, poly(thiophene)s, andpoly(ethyloxazoline)s

ultrasound: ethylenevinylacetate

These transitions are reversible and include changes in physical state,shape and solubility, solvent interactions, hydrophilic and lipophilicbalances and conductivity. The driving forces behind these transitionsinclude neutralisation of charged groups by the addition of oppositelycharged polymers or by pH shift, and change in thehydrophilic/lipophilic balance or changes in hydrogen bonding due toincrease or decrease in temperature. Responses of a stimulus-responsivepolymer can be of various types. Responsiveness of a polymeric solutioninitiated by physical or chemical stimuli is limited to the destructionand formation of various secondary forces including hydrogen bonding,hydrophobic forces, van der Waals forces and electrostatic interaction.Chemical events include simple reactions such as oxidation, acid-basereaction, reduction and hydrolysis of moieties attached to the polymerchain. In some cases, dramatic conformational change in the polymericstructure occurs, e.g., degradation of the polymeric structure due toirreversible bond breakage in response to an external stimulus. Uponexposure to appropriate stimuli, some exemplary physicochemicalproperties include size, zeta potential and hydrophilic-hydrophobicbalance of these nanoparticles.

pH Dependent Polymers

Exemplary pH dependent polymers include dendrimers formed ofpoly(lysine), poly(hydroxyproline), PEG-PLA, Poly(propyl acrylic acid),Poly(ethacrylic acid), CARBOPOLL®, Polysilamine, EUDRAGIT® S-100EUDRAGIT® L-100, Chitosan, PMAA-PEG copolymer, sodium alginate (Ca2+).The ionic pH sensitive polymers are able to accept or release protons inresponse to pH changes. These polymers contain acid groups (carboxylicor sulfonic) or basic groups (ammonium salts) so that the pH sensitivepolymers are polyelectrolytes that have in their structure acid or basicgroups that can accept or release protons in response to pH changes inthe surrounding environment. pH values from several tissues and cellcompartments can be used to trigger release in these tissues. Forexample, the pH of blood is 7.4-7.5; stomach is 1.0-3.0; duodenum is4.8-8.2; colon is 7.0-7.5; lysosome is 4.5-5.0; Golgi complex is 6.4;tumor—extracellular médium is 6.2-7.2.

Examples of these polymers include polyacrylamide (PAAm), poly(acrylicacid) (PAA) (CARBOPOL1®) and derivatives, poly(methacrylic acid) (PMAA),poly(2-diethylaminoethyl methacrylate) (PDEAEMA), poly(ethylene imine),poly(L-lysine) and poly(N,N-dimethylaminoethylmetha crylate) (PDMAEMA).Polymers with functional acid groups pH sensitive polymers includepoly(acrylic acid) (PAA) or poly(methacrylic) acid (PMAA) are polyanionsthat have in their structure a great number of ionizable acid groups,like carboxylic acid or sulfonic acid. The pH in which acids becomeionized depends on the polymer's pKa (depends on the polymer'scomposition and molecular weight). Polymers with functional basic groupsinclude polycations such as poly(4-vinylpyridine), poly(2-vinylpyridine)(PVP) and poly(vinylamine) (PVAm), are protonated at high pH values andpositively ionized at neutral or low pH values, i.e., they go through aphase transition at pH 5 due to the deprotonation of the pyridinegroups. Other polybases are poly(N,N-dimethylaminoethyl methacrylate)(PDMAEMA) and poly(2-diethylaminoethyl methacrylate) (PDEAEMA), withamino groups in their structure which in acid environments gain protons,and in basic environments release the protons. Examples of polycationicpolyelectrolyte polymers are poly(N,N-diakyl aminoethyl methacrylate),poly(lysine) (PL), poly(ethylenimine) (PEI) and chitosan. Commerciallyavailable polymers include EUDRAGIT L® and EUDRAGIT S® from Röhm PharmaGmBH (with methacrylic acid and methylmethacrylate in theircomposition), CMEC (a cellulose derivative) from Freund Sangyo Co., CAPby Wako Pure Chemicals Ltd., HP-50 and ASM by Shin-Etsu Chemical Co.,Ltd.

There are several natural polymers (for example, albumin, gelatin andchitosan) that present pH sensibility. Chitosan is a cationic aminopolysaccharide, derivative from chitin, that is biocompatible andresorbable. Additional examples include the anionic polymer PEAA(polyethacrylic acid) or by PPAA (polypropyl acrylic acid),Polypropylacrylic acid (PPAA) and polyethacrylic acid (PEAA), andpoly(ethylene glycol)-poly(aspartame hydrazine doxorubicin)[(PEG-p(Asp-Hid-dox), and polycationic polymers, such aspoly(2-diethylaminoethyl methacrylate) (PDEAEMA).

In one embodiment, the pH-sensitive polymer is poly(2-(diisopropylamino) ethylmethacrylate (PDPA),poly(2-(hexamethyleneimino) ethyl methacrylate (PHMEMA), or PEGylatedderivatives, and/or copolymers thereof. Examplary PEGylated derivativesand copolymers include Meo-PEG-b-PDPA, methoxyl-polyethyleneglycol-b-poly (2-(diisopropylamino) ethylmethacrylate-co-glycidylmethacrylate) (Meo-PEG-b-P(DPA-co-GMA)),Meo-PEG-b-P(DPA-co-GMA-TEPA-C14), Meo-PEG-b-P(DPA-co-GMA-R_(n)),Meo-PEG-b-P(DPA-co-GMA-TEPA), methoxyl-polyethyleneglycol-b-poly(2-(hexamethyleneimino) ethyl methacrylate)(Meo-PEG-b-PHMEMA), and Meo-PEG-b-P(HMEMA-co-AMA).

Temperature Dependent Polymers

Temperature dependent polymers are sensitive to the temperature andchange their microstructural features in response to change intemperature. Thermo-responsive polymers present in their structure avery sensitive balance between the hydrophobic and the hydrophilicgroups and a small change in the temperature can create new adjustments.If the polymeric solution has a phase below the critical solutiontemperature, it will become insoluble after heating. Above the criticalsolution temperature (LCST), the interaction strengths (hydrogenlinkages) between the water molecules and the polymer becomeunfavorable, it dehydrates and a predominance of the hydrophobicinteraction occurs, causing the polymer to swell. The LSCT is thecritical temperature in which the polymeric solution shows a phaseseparation, going from one phase (isotropic state) to two phases(anisotropic state). The accumulation of temperature sensitive polymericsystems in solid tumors is due to the increased impermeability effect tothe tumor vascular net retention and to the use of an external impulse(heat source) on the tumor area. This temperature increase promotes thechanging of the microstructure of the polymeric system, turning it intogel and releasing the drug, thus increasing the drug in theintra-tumoral area and the therapeutic efficiency, and reducing the sideeffects (MacEwan et al., 2010).

Examples of thermosensitive polymers include the poly(N-substitutedacrylamide) polymers such as poly(N-isopoprylacrilamide) (PNIPAAm), poly(N,N′-diethyl acrylamide), poly (dimethylamino ethyl methacrylate andpoly (N-(L)-(1-hydroxymethyl) propyl methacrylamide). Other examples ofthermo-responsive polymers are: copolymers blocks of poly(ethyleneglycol)/poly(lactide-coglicolide) (PEG/PLGA, REGEL®),polyoxyethylenepolyoxypropylene (PEO/PPO), triple blocks of copolymerspolyoxyethylene-polyoxypropylene-polyoxyethylene (PEO-PPOPEO) andpoly(ethylene glycol)-poly(lactic acid)-poly(ethylene glycol)(PEG-PLA-PEG). Exemplary polymers and their LCST: PNIPAAm, LCST 32° C.;PDEAAm, LCST 26-35° C.; PDMAEMA, LCST 50° C.;poly(N-(L)-(hydroxymethyl)propylmethacrylamide), LCST 30° C.

An increase of the hydrophobic monomers (as, for example, the butylmethacrylate) or on the molecular weight, results in a LCST decrease(Jeong, Gutowska, 2002). The incorporation of hydrophilic monomers suchas acrylic acid or hydroxyethyl methacrylate) fosters the creation ofincreases LCST. The co-polymers NIPAAm conjugated with hydrophilicunities such as acrylic acid promotes the increase of LCST totemperatures around 37° C., i.e., the body temperature. Polymers with2-hydroxyethyl (methacrylate) (HEMA) promote the increase of LCST abovethe body temperature

POLOXAMERs and derivatives are well known temperature sensitivepolymers. The copolymer blocks based on PEO-PPO sequences constitutesone family of triple blocks of commercialized copolymers with thefollowing names: PLURONICS®, POLOXAMERS® AND TETRONICS®. POLOXAMERS® arenon-ionic polymers polyoxyethylenepolyoxypropylene-polyoxyethylene(PEOn-PPOn-PEOn), with many pharmaceutical uses (Ricci et al., 2005).The triple block of copolymers PEO—PPO-PEO (PLURONICS® or POLOXAMERS®)get into gel at body temperature in concentrations above 15% (m/m). ThePOLOXAMERs® normally used are: 188 (F-68), 237 (F-87), 338 (F-108) and407 (F-127). “F” refers to the polymer in the form of flakes. PLURONICS®and TETRONICS® are polymers approved by FDA to be used as foodadditives, pharmaceutical ingredients, drug carriers in parenteralsystems, tissue engineering and agricultural products. PLURONIC F-127(Polaxamer 407, PF-127) can also be used as carrier in several routes ofadministration, including oral, cutaneous, intranasal, vaginal, rectal,ocular and parenteral. PLURONIC® F127 (PF-127) or POLOXAMER 407 (P407)(copolymer polyoxyethylene 106-polyoxypropylene 70-polyoxyethylene106)contains about 70% of ethylene oxide which contributes to itshydrophilicity.

Polymers with Dual Stimuli-Responsiveness

To obtain a temperature and pH sensitive polymer it is only necessary tocombine temperature sensitive monomers (as, for example,poly(N-isopropylacrylamide-co-methacrylic acid and PNIPAm) with pHsensitive monomers (as, for example, AA and MAA).

Polymers with Binding or Biological Responsiveness Biologicallyresponsive polymer systems are increasingly important in variousbiomedical applications. The major advantage of bioresponsive polymersis that they can respond to the stimuli that are inherently present inthe natural system. Bioresponsive polymeric systems mainly arise fromcommon functional groups that are known to interact with biologicallyrelevant species, and in other instances the synthetic polymer isconjugated to a biological component. Bioresponsive polymers areclassified into antigen-responsive polymers, glucose-sensitive polymers,and enzyme-responsive polymers.

Glucose-responsive polymeric-based systems have been developed based onthe following approaches: enzymatic oxidation of glucose by glucoseoxidase, and binding of glucose with lectin or reversible covalent bondformation with phenylboronic acid moieties. Glucose sensitivity occursby the response of the polymer toward the byproducts that result fromthe enzymatic oxidation of glucose. Glucose oxidase oxidises glucoseresulting in the formation of gluconic acid and H₂O₂. For example, inthe case of poly (acrylicacid) conjugated with the GOx system, as theblood glucose level is increased glucose is converted into gluconic acidwhich causes the reduction of pH and protonation of PAA carboxylatemoieties, facilitating the release of insulin. Another system utilizesthe unique carbohydrate binding properties of lectin for the fabricationof a glucose-sensitive system. Concanavalin A (Con A) is a lectinpossessing four binding sites and has been used frequently ininsulin-modulated drug delivery. In this type of system the insulinmoiety is chemically modified by introducing a functional group (orglucose molecule) and then attached to a carrier or support throughspecific interactions which can only be interrupted by the glucoseitself. The glycosylated insulin-Con A complex exploits the competitivebinding behaviour of Con A with glucose and glycosylated insulin. Thefree glucose molecule causes the displacement of glycosylated ConA-insulin conjugates.

Another approach includes polymers with phenylboronic groups and polyolpolymers that form a gel through complex formation between the pendantphenylborate and hydroxyl groups. Instead of polyol polymers, shortmolecules such as diglucosylhexadiamine have been used. As the glucoseconcentration increases, the crosslinking density of the gel decreasesand as a result insulin is released from the eroded gel. The glucoseexchange reaction is reversible and reformation of the gel occurs as aresult of borate-polyol crosslinking.

Field-responsive polymers respond to the application of electric,magnetic, sonic or electromagnetic fields. The additional benefit overtraditional stimuli-sensitive polymers is their fast response time,anisotropic deformation due to directional stimuli, and also acontrolled drug release rate simply by modulating the point of signalcontrol.

Light-Sensitive Polymers

A light-sensitive polymer undergoes a phase transition in response toexposure to light. These polymers can be classified into UV-sensitiveand visible-sensitive systems on the basis of the wavelength of lightthat triggers the phase transition.

A variety of materials are known, such as a leuco-derivative molecule,bis(4-dimethylamino)phenylmethyl leucocyanide, which undergoes phasetransition behaviour in response to UV light. Triphenylmethane-leucoderivatives dissociate into ion-pairs such as triphenylmethyl cationsupon UV irradiation. At a fixed temperature these hydrogels swelldiscontinuously due to increased osmotic pressure in response to UVirradiation but shrink when the stimulus is removed. Another example isa thermosensitive diarylated pluronic F-127.

Visible light-sensitive polymeric materials can be prepared byincorporating photosensitive molecules such as chromophores (e.g.,trisodium salt of copper chlorophyllin). When light of appropriatewavelength is applied, the chromophore absorbs light which is thendissipated locally as heat by radiationless transition, increasing thelocal temperature of the polymeric material, leading to alteration ofthe swelling behavior. The temperature increase directly depends on thechromophore concentration and light intensity.

Electric Field-Sensitive Polymers

Electric field-sensitive polymers change their physical properties inresponse to a small change in electric current. These polymers contain arelatively large concentration of ionisable groups along the back bonechain that are also pH-responsive. Electro-responsive polymers transformelectric energy into mechanical energy. The electric current causes achange in pH which leads to disruption of hydrogen bonding betweenpolymer chains, causing degradation or bending of the polymer chain.Major mechanisms involved in drug release from electro-responsivepolymer are diffusion, electrophoresis of charged drug, forcedconvection of drug out of the polymer or degradation of the polymer.

Naturally occurring polymers such as chitosan, alginate and hyalouronicacid are commonly employed to prepare electro-responsive materials.Major synthetic polymers that have been used include allyl amine, vinylalcohol, acrylonitrile, methacrylic acid and vinylacrylic acid. In somecases, combinations of natural and synthetic polymers have been used.Most polymers that exhibit electro-sensitive behavior arepolyelectrolytes and undergo deformation under an electric field due toanisotropic swelling or deswelling as the charged ions move towards thecathode or anode. Neutral polymers that exhibit electro-sensitivebehavior require the presence of a polarisable component with theability to respond to the electric field. Another example of a materialwhich can be used is poly(2-acrylamido-2-methylpropane sulphonicacid-co-n-butylmethacrylate).

B. Active Agents

In some embodiments, the NPs contain between about 1% and about 70%weight/weight of a therapeutic agent, a prophylactic agent, a diagnosticagent, or combinations thereof. Preferably, the NPs contain betweenabout 5% and about 50% weight/weight, most preferably between about 10%and about 30% weight/weight of a therapeutic agent, a prophylacticagent, a diagnostic agent, or combinations thereof.

Active agent cargos to be delivered include therapeutic, nutritional,diagnostic, and prophylactic agents. The active agents can be smallmolecule active agents or biomacromolecules, such as proteins,polypeptides, sugars or carbohydrates, lipids, nucleic acids or smallmolecule compounds (typically 1 kD or less, but may be larger). Suitablesmall molecule active agents include organic and organometalliccompounds. The small molecule active agents can be a hydrophilic,hydrophobic, or amphiphilic compound.

Active agents include synthetic and natural proteins (including enzymes,peptide-hormones, receptors, growth factors, antibodies, signalingmolecules), and synthetic and natural nucleic acids (including RNA, DNA,anti-sense RNA, triplex DNA, inhibitory RNA (RNAi), andoligonucleotides), and biologically active portions thereof. Suitableactive agents have a size greater than about 1,000 Da for small peptidesand polypeptides, more typically at least about 5,000 Da and often10,000 Da or more for proteins. Nucleic acids are more typically listedin terms of base pairs or bases (collectively “bp”). Nucleic acids withlengths above about 10 bp are typically used. More typically, usefullengths of nucleic acids for probing or therapeutic use will be in therange from about 20 bp (probes; inhibitory RNAs, etc.) to tens ofthousands of bp for genes and vectors. The active agents may also behydrophilic molecules, preferably having a low molecular weight.

Exemplary therapeutic agents that can be incorporated into particlesinclude tumor antigens, CD4+ T-cell epitopes, cytokines,chemotherapeutic agents, radionuclides, small molecule signaltransduction inhibitors, photothermal antennas, monoclonal antibodies,immunologic danger signaling molecules, other immunotherapeutics,enzymes, antibiotics, antivirals (especially protease inhibitors aloneor in combination with nucleosides for treatment of HIV or Hepatitis Bor C), anti-parasites (helminths, protozoans), growth factors, growthinhibitors, hormones, hormone antagonists, antibodies and bioactivefragments thereof (including humanized, single chain, and chimericantibodies), antigen and vaccine formulations (including adjuvants),peptide drugs, anti-inflammatories, immunomodulators (including ligandsthat bind to Toll-Like Receptors (including, but not limited to, CpGoligonucleotides) to activate the innate immune system, molecules thatmobilize and optimize the adaptive immune system, molecules thatactivate or up-regulate the action of cytotoxic T lymphocytes, naturalkiller cells and helper T-cells, and molecules that deactivate ordown-regulate suppressor or regulatory T-cells), agents that promoteuptake of particles into cells, nutraceuticals such as vitamins, andoligonucleotide drugs (including DNA, RNAs, antisense, aptamers, smallinterfering RNAs, ribozymes, external guide sequences for ribonucleaseP, and triplex forming agents).

Exemplary diagnostic agents include paramagnetic molecules, fluorescentcompounds, magnetic molecules, and radionuclides, x-ray imaging agents,and contrast agents.

As discussed in more detail below, in some embodiments, the particlesinclude one or more anti-cancer agents.

In certain embodiments, the particle includes one or moreimmunomodulatory agents. Exemplary immunomodulatory agents includecytokines, xanthines, interleukins, interferons, oligodeoxynucleotides,glucans, growth factors (e.g., TNF, CSF, GM-CSF and G-CSF), hormonessuch as estrogens (diethylstilbestrol, estradiol), androgens(testosterone, HALOTESTIN® (fluoxymesterone)), progestins (MEGACE®(megestrol acetate), PROVERA® (medroxyprogesterone acetate)), andcorticosteroids (prednisone, dexamethasone, hydrocortisone).

Examples of immunological adjuvants that can be associated with theparticles include, but are not limited to, TLR ligands, C-Type LectinReceptor ligands, NOD-Like Receptor ligands, RLR ligands, and RAGEligands. TLR ligands can include lipopolysaccharide (LPS) andderivatives thereof, as well as lipid A and derivatives there ofincluding, but not limited to, monophosphoryl lipid A (MPL),glycopyranosyl lipid A, PET-lipid A, and 3-O-desacyl-4′-monophosphoryllipid A. In a specific embodiment, the immunological adjuvant is MPL. Inanother embodiment, the immunological adjuvant is LPS. TLR ligands canalso include, but are not limited to, TLR3 ligands (e.g.,polyinosinic-polycytidylic acid (poly(I:C)), TLR7 ligands (e.g.,imiquimod and resiquimod), and TLR9 ligands.

The particles may also include antigens and/or adjuvants (i.e.,molecules enhancing an immune response). Peptide, protein, and DNA basedvaccines may be used to induce immunity to various diseases orconditions. Cell-mediated immunity is needed to detect and destroyvirus-infected cells. Most traditional vaccines (e.g. protein-basedvaccines) can only induce humoral immunity. DNA based vaccine can induceboth humoral and cell-mediated immunity. DNA vaccines are relativelymore stable and more cost-effective for manufacturing and storage. DNAvaccines consist of two major components, DNA carriers (or deliveryvehicles) and DNAs encoding antigens. DNA carriers protect DNA fromdegradation, and can facilitate DNA entry to specific tissues or cellsand expression at an efficient level.

Under the Biopharmaceutical Classification System (BCS), drugs canbelong to four classes: class I (high permeability, high solubility),class II (high permeability, low solubility), class III (lowpermeability, high solubility) or class IV (low permeability, lowsolubility). Suitable active agents also include poorly solublecompounds; such as drugs that are classified as class II or class IVcompounds using the BCS. Examples of class II compounds include:acyclovir, nifedipine, danazol, ketoconazole, mefenamic acid,nisoldipine, nicardipine, felodipine, atovaquone, griseofulvin,troglitazone glibenclamide and carbamazepine. Examples of class IVcompounds include: chlorothiazide, furosemide, tobramycin, cefuroxmine,and paclitaxel.

An imaging, detectable or sensing moiety, i.e., a moiety that can bedetermined in some fashion, either directly or indirectly, may be boundto the NPs or to the polymers forming the NPs, or encapsulated therein.Representative imaging entities include, but are not limited to,fluorescent, radioactive, electron-dense, magnetic, or labeled membersof a binding pair or a substrate for an enzymatic reaction, which can bedetected. In some cases, the imaging entity itself is not directlydetermined, but instead interacts with a second entity in order toeffect determination; for example, coupling of the second entity to theimaging entity may result in a determinable signal. Non-limitingexamples of imaging moieties include, but are not limited to,fluorescent compounds such as FITC or a FITC derivative, fluorescein,green fluorescent protein (“GFP”), radioactive atoms such as ³H, ¹⁴C,³³P, ³²P, ¹²⁵I, ¹³¹I, ³⁵S, or a heavy metal species, for example, goldor osmium. As a specific example, an imaging moiety may be a goldnanoparticle. A diagnostic or imaging tag such as a fluorescent tag ischemically conjugated to a polymer to yield a fluorescently labeledpolymer.

For imaging, radioactive materials such as Technetium99 (^(99m)Tc) ormagnetic materials such as Fe₂O₃ could be used. Examples of othermaterials include gases or gas emitting compounds, which areradioopaque.

1. Nucleic Acid-Based Active Agents

The cargo can be a nucleic acid. An isolated nucleic acid can be, forexample, a DNA, an RNA, or a nucleic acid analog. Nucleic acid analogscan be modified at the base moiety, sugar moiety, or phosphate backbone.Such modification can improve, for example, stability, hybridization, orsolubility of the nucleic acid. Exemplary modifications include,2′O-methyl, 2′ methoxy-ethyl, phosphoramidate, methylphosphonate, and/orphosphorothioate backbone chemistry. Other mon-limiting modificationsare discussed in more detail below. The nucleic acid molecule can existas a separate molecule independent of other sequences (e.g., achemically synthesized nucleic acid, or a cDNA or genomic DNA fragmentproduced by PCR or restriction endonuclease treatment), as well asrecombinant DNA that is incorporated into a vector, an autonomouslyreplicating plasmid, a virus (e.g., a retrovirus, lentivirus,adenovirus, or herpes virus), etc. The nucleic acid can be an engineerednucleic acid such as a recombinant DNA molecule that is part of a hybridor fusion nucleic acid.

The genetic material to be loaded into the particles is chosen on thebasis of the desired effect of that genetic material on the cell intowhich it is intended to be delivered and the mechanism by which thateffect is to be carried out. For example, the nucleic acid may be usefulin gene therapy, for example in order to express a desired gene in acell or group of cells. Nucleic acid can also be used in gene silencing.Such gene silencing may be useful in therapy to switch off aberrant geneexpression. Nucleic acid can also be used for example to express one ormore antigens against which it is desired to produce an immune response.Thus, the nucleic acid to be loaded into the particle can encode one ormore antigens against which is desired to produce an immune response,including but not limited to tumour antigens, antigens from pathogenssuch as viral, bacterial or fungal pathogens, such as those discussed inmore detail below. Therapeutic strategies for treating cancer,inflammation, injury, autoimmunity, and infections are discussed in moredetail below.

a. Functional Nucleic Acids

In some embodiments, the active agent cargo is a functional nucleicacid. Functional nucleic acids are nucleic acid molecules that have aspecific function, such as binding a target molecule or catalyzing aspecific reaction. As discussed in more detail below, functional nucleicacid molecules can be divided into the following non-limitingcategories: antisense molecules, RNAi including siRNA, miRNA, and piRNA,aptamers, ribozymes, triplex forming molecules, external guidesequences, and gene editing compositions. The functional nucleic acidmolecules can act as effectors, inhibitors, modulators, and stimulatorsof a specific activity possessed by a target molecule, or the functionalnucleic acid molecules can possess a de novo activity independent of anyother molecules.

Functional nucleic acid molecules can interact with any macromolecule,such as DNA, RNA, polypeptides, or carbohydrate chains. Thus, functionalnucleic acids can interact with the mRNA or the genomic DNA of a targetpolypeptide or they can interact with the polypeptide itself. Oftenfunctional nucleic acids are designed to interact with other nucleicacids based on sequence homology between the target molecule and thefunctional nucleic acid molecule. In other situations, the specificrecognition between the functional nucleic acid molecule and the targetmolecule is not based on sequence homology between the functionalnucleic acid molecule and the target molecule, but rather is based onthe formation of tertiary structure that allows specific recognition totake place.

i. Antisense

The functional nucleic acids can be antisense molecules. Antisensemolecules are designed to interact with a target nucleic acid moleculethrough either canonical or non-canonical base pairing. The interactionof the antisense molecule and the target molecule is designed to promotethe destruction of the target molecule through, for example, RNAse Hmediated RNA-DNA hybrid degradation. Alternatively the antisensemolecule is designed to interrupt a processing function that normallywould take place on the target molecule, such as transcription orreplication. Antisense molecules can be designed based on the sequenceof the target molecule. There are numerous methods for optimization ofantisense efficiency by finding the most accessible regions of thetarget molecule. Exemplary methods include in vitro selectionexperiments and DNA modification studies using DMS and DEPC. It ispreferred that antisense molecules bind the target molecule with adissociation constant (K_(d)) less than or equal to 10⁻⁶, 10⁻⁸, 10⁻¹⁰,or 10⁻¹².

ii. Aptamers

The functional nucleic acids can be aptamers. Aptamers are moleculesthat interact with a target molecule, preferably in a specific way.Typically aptamers are small nucleic acids ranging from 15-50 bases inlength that fold into defined secondary and tertiary structures, such asstem-loops or G-quartets. Aptamers can bind small molecules, such as ATPand theophiline, as well as large molecules, such as reversetranscriptase and thrombin. Aptamers can bind very tightly with K_(d)'sfrom the target molecule of less than 10⁻¹² M. It is preferred that theaptamers bind the target molecule with a K_(d) less than 10⁻⁶, 10⁻⁸,10⁻¹⁰, or 10⁻¹². Aptamers can bind the target molecule with a very highdegree of specificity. For example, aptamers have been isolated thathave greater than a 10,000 fold difference in binding affinities betweenthe target molecule and another molecule that differ at only a singleposition on the molecule. It is preferred that the aptamer have a K_(d)with the target molecule at least 10, 100, 1000, 10,000, or 100,000 foldlower than the K_(d) with a background binding molecule. It is preferredwhen doing the comparison for a molecule such as a polypeptide, that thebackground molecule be a different polypeptide.

iii. Ribozymes

The functional nucleic acids can be ribozymes. Ribozymes are nucleicacid molecules that are capable of catalyzing a chemical reaction,either intramolecularly or intermolecularly. It is preferred that theribozymes catalyze intermolecular reactions. There are a number ofdifferent types of ribozymes that catalyze nuclease or nucleic acidpolymerase type reactions which are based on ribozymes found in naturalsystems, such as hammerhead ribozymes. There are also a number ofribozymes that are not found in natural systems, but which have beenengineered to catalyze specific reactions de novo. Preferred ribozymescleave RNA or DNA substrates, and more preferably cleave RNA substrates.Ribozymes typically cleave nucleic acid substrates through recognitionand binding of the target substrate with subsequent cleavage. Thisrecognition is often based mostly on canonical or non-canonical basepair interactions. This property makes ribozymes particularly goodcandidates for target specific cleavage of nucleic acids becauserecognition of the target substrate is based on the target substratessequence.

iv. Triplex Forming Oligonucleotides

The functional nucleic acids can be triplex forming molecules. Triplexforming functional nucleic acid molecules are molecules that caninteract with either double-stranded or single-stranded nucleic acid.When triplex molecules interact with a target region, a structure calleda triplex is formed in which there are three strands of DNA forming acomplex dependent on both Watson-Crick and Hoogsteen base-pairing.Triplex molecules are preferred because they can bind target regionswith high affinity and specificity. It is preferred that the triplexforming molecules bind the target molecule with a K_(d) less than 10⁻⁶,10⁻⁸, 10⁻¹⁰, or 10⁻¹².

v. External Guide Sequences

The functional nucleic acids can be external guide sequences. Externalguide sequences (EGSs) are molecules that bind a target nucleic acidmolecule forming a complex, which is recognized by RNase P, which thencleaves the target molecule. EGSs can be designed to specifically targetan RNA molecule of choice. RNAse P aids in processing transfer RNA(tRNA) within a cell. Bacterial RNAse P can be recruited to cleavevirtually any RNA sequence by using an EGS that causes the targetRNA:EGS complex to mimic the natural tRNA substrate. Similarly,eukaryotic EGS/RNAse P-directed cleavage of RNA can be utilized tocleave desired targets within eukarotic cells. Representative examplesof how to make and use EGS molecules to facilitate cleavage of a varietyof different target molecules are known in the art.

vi. RNA Interference

In some embodiments, the functional nucleic acids induce gene silencingthrough RNA interference. Gene expression can also be effectivelysilenced in a highly specific manner through RNA interference (RNAi),which can generally be divided into three major classes based on theirprocessing mechanisms and partner Argonaute proteins: micro RNAs(miRNAs), small interfering RNAs (siRNAs), and PIWI-interacting RNA(piRNAs) (Czech and Hannon, Trends Biochem Sci., 2016 Jan. 19. pii:S0968-0004(15)00258-3. doi: 10.1016/j.tibs.2015.12.008. [Epub ahead ofprint].

RNAi silencing was originally observed with the addition of doublestranded RNA (dsRNA) (Fire, et al. (1998) Nature, 391:806-11; Napoli, etal. (1990) Plant Cell 2:279-89; Hannon, (2002) Nature, 418:244-51). OncedsRNA enters a cell, it is cleaved by an RNase III—like enzyme, Dicer,into double stranded small interfering RNAs (siRNA) 21-23 nucleotides inlength that contains 2 nucleotide overhangs on the 3′ ends (Elbashir, etal. (2001) Genes Dev., 15:188-200; Bernstein, et al. (2001) Nature,409:363-6; Hammond, et al. (2000) Nature, 404:293-6). In an ATPdependent step, the siRNAs become integrated into a multi-subunitprotein complex, commonly known as the RNAi induced silencing complex(RISC), which guides the siRNAs to the target RNA sequence (Nykanen, etal. (2001) Cell, 107:309-21). At some point the siRNA duplex unwinds,and it appears that the antisense strand remains bound to RISC anddirects degradation of the complementary mRNA sequence by a combinationof endo and exonucleases (Martinez, et al. (2002) Cell, 110:563-74).However, the effect of iRNA or siRNA or their use is not limited to anytype of mechanism.

Short Interfering RNA (siRNA) is a double-stranded RNA that can inducesequence-specific post-transcriptional gene silencing, therebydecreasing or even inhibiting gene expression. In one example, a siRNAtriggers the specific degradation of homologous RNA molecules, such asmRNAs, within the region of sequence identity between both the siRNA andthe target RNA. For example, WO 02/44321 discloses siRNAs capable ofsequence-specific degradation of target mRNAs when base-paired with 3′overhanging ends, herein incorporated by reference for the method ofmaking these siRNAs.

Sequence specific gene silencing can be achieved in mammalian cellsusing synthetic, short double-stranded RNAs that mimic the siRNAsproduced by the enzyme dicer (Elbashir, et al. (2001) Nature, 411:494498) (Ui-Tei, et al. (2000) FEBS Lett 479:79-82). siRNA can bechemically or in vitro-synthesized or can be the result of shortdouble-stranded hairpin-like RNAs (shRNAs) that are processed intosiRNAs inside the cell. Synthetic siRNAs are generally designed usingalgorithms and a conventional DNA/RNA synthesizer. Suppliers includeAmbion (Austin, Tex.), ChemGenes (Ashland, Mass.), Dharmacon (Lafayette,Colo.), Glen Research (Sterling, Va.), MWB Biotech (Esbersberg,Germany), Proligo (Boulder, Colo.), and Qiagen (Vento, The Netherlands).siRNA can also be synthesized in vitro using kits such as Ambion'sSILENCER® siRNA Construction Kit.

The production of siRNA from a vector is more commonly done through thetranscription of a short hairpin RNAse (shRNAs). Kits for the productionof vectors comprising shRNA are available, such as, for example,Imgenex's GENESUPPRESSOR™ Construction Kits and Invitrogen's BLOCK-IT™inducible RNAi plasmid and lentivirus vectors.

Micro RNAs (abbreviated miRNA) are small non-coding RNA molecules(containing about 22 nucleotides) that functions in RNA silencing andpost-transcriptional regulation of gene expression. miRNAs resemblesiRNAs of the RNA interference (RNAi) pathway, except miRNAs derive fromregions of RNA transcripts that fold back on themselves to form shorthairpins, whereas siRNAs derive from longer regions of double-strandedRNA (Bartel, et al., Cell, 116:281-297 (2004)).

The biogenesis of miRNAs and siRNAs typically depends on RNase III typeenzymes that convert their double-stranded RNA precursors intofunctional small RNAs. By contrast, piRNAs derive from single-strandedRNAs and, consequently, require alternative processing machinery.

Synthetic piRNAs can be used to block the synthesis of target proteinsby binding to mRNAs, as has been attempted with miRNAs, might have theadvantage of not requiring processing by enzymes such as Dicer, which isrequired by miRNAs. Additional speculative advantages of piRNAs overmiRNAs include the possibility of targets with better specificitybecause each miRNA regulates several mRNAs and there is the potential toaccess undesirable long non-coding RNAs with possible implications indisease processes (Assumpção, et al., Epigenomics, 7(6):975-984 (2015)).miRNA and piRNA can be the therapeutic agent or can be target sequencesfor post-transcriptional silencing. For example, synthetic piRNAsdesigned to couple to PIWI proteins and exert genomic silencing on PIWIgenes at a transcriptional level is a possible strategy.

In some embodiment, the functional nucleic acid is siRNA, shRNA, miRNA,or piRNA. In some embodiments, the composition includes a vectorexpressing the functional nucleic acid. Methods of making and usingvectors for in vivo expression of functional nucleic acids such asantisense oligonucleotides, siRNA, shRNA, miRNA, piRNA, EGSs, ribozymes,and aptamers are known in the art.

vii. Other Gene Editing Compositions

In some embodiments the functional nucleic acids are gene editingcompositions. Gene editing compositions can include nucleic acids thatencode an element or elements that induce a single or a double strandbreak in the target cell's genome, and optionally a polynucleotide. Thecompositions can be used, for example, to reduce or otherwise modifyexpression of a gene target.

1. Strand Break Inducing Elements

It will be appreciated that some of the embodiments discussed belowinclude protein active agents. In some embodiments, the agents arepackaged into particles as nucleic acids encoding the proteins (e.g.,mRNA, expression vectors, etc.).

CRISPR/Cas

In some embodiments, the element that induces a single or a doublestrand break in the target cell's genome is a CRISPR/Cas system. CRISPR(Clustered Regularly Interspaced Short Palindromic Repeats) is anacronym for DNA loci that contain multiple, short, direct repetitions ofbase sequences. The prokaryotic CRISPR/Cas system has been adapted foruse as gene editing (silencing, enhancing or changing specific genes)for use in eukaryotes (see, for example, Cong, Science,15:339(6121):819-823 (2013) and Jinek, et al., Science, 337(6096):816-21(2012)). By transfecting a cell with the required elements including acas gene and specifically designed CRISPRs, the organism's genome can becut and modified at any desired location. Methods of preparingcompositions for use in genome editing using the CRISPR/Cas systems aredescribed in detail in WO 2013/176772 and WO 2014/018423, which arespecifically incorporated by reference herein in their entireties.

In general, “CRISPR system” refers collectively to transcripts and otherelements involved in the expression of or directing the activity ofCRISPR-associated (“Cas”) genes, including sequences encoding a Casgene, a tracr (trans-activating CRISPR) sequence (e.g., tracrRNA or anactive partial tracrRNA), a tracr-mate sequence (encompassing a “directrepeat” and a tracrRNA-processed partial direct repeat in the context ofan endogenous CRISPR system), a guide sequence (also referred to as a“spacer” in the context of an endogenous CRISPR system), or othersequences and transcripts from a CRISPR locus. One or more tracr matesequences operably linked to a guide sequence (e.g., directrepeat-spacer-direct repeat) can also be referred to as pre-crRNA(pre-CRISPR RNA) before processing or crRNA after processing by anuclease.

In some embodiments, a tracrRNA and crRNA are linked and form a chimericcrRNA-tracrRNA hybrid where a mature crRNA is fused to a partialtracrRNA via a synthetic stem loop to mimic the natural crRNA:tracrRNAduplex as described in Cong, Science, 15:339(6121):819-823 (2013) andJinek, et al., Science, 337(6096):816-21 (2012)). A single fusedcrRNA-tracrRNA construct can also be referred to as a guide RNA or gRNA(or single-guide RNA (sgRNA)). Within an sgRNA, the crRNA portion can beidentified as the ‘target sequence’ and the tracrRNA is often referredto as the ‘scaffold’.

There are many resources available for helping practitioners determinesuitable target sites once a desired DNA target sequence is identified.For example, numerous public resources, including a bioinformaticallygenerated list of about 190,000 potential sgRNAs, targeting more than40% of human exons, are available to aid practitioners in selectingtarget sites and designing the associate sgRNA to affect a nick ordouble strand break at the site. See also, crispr.u-psud.fr/, a tooldesigned to help scientists find CRISPR targeting sites in a wide rangeof species and generate the appropriate crRNA sequences.

In some embodiments, one or more vectors driving expression of one ormore elements of a CRISPR system are introduced into a target cell suchthat expression of the elements of the CRISPR system direct formation ofa CRISPR complex at one or more target sites. While the specifics can bevaried in different engineered CRISPR systems, the overall methodologyis similar. A practitioner interested in using CRISPR technology totarget a DNA sequence can insert a short DNA fragment containing thetarget sequence into a guide RNA expression plasmid. The sgRNAexpression plasmid contains the target sequence (about 20 nucleotides),a form of the tracrRNA sequence (the scaffold) as well as a suitablepromoter and necessary elements for proper processing in eukaryoticcells. Such vectors are commercially available (see, for example,Addgene). Many of the systems rely on custom, complementary oligos thatare annealed to form a double stranded DNA and then cloned into thesgRNA expression plasmid. Co-expression of the sgRNA and the appropriateCas enzyme from the same or separate plasmids in transfected cellsresults in a single or double strand break (depending of the activity ofthe Cas enzyme) at the desired target site.

Zinc Finger Nucleases

In some embodiments, the element that induces a single or a doublestrand break in the target cell's genome is a nucleic acid construct orconstructs encoding a zinc finger nucleases (ZFNs). ZFNs are typicallyfusion proteins that include a DNA-binding domain derived from azinc-finger protein linked to a cleavage domain.

The most common cleavage domain is the Type IIS enzyme Fokl. Foklcatalyzes double-stranded cleavage of DNA, at 9 nucleotides from itsrecognition site on one strand and 13 nucleotides from its recognitionsite on the other. See, for example, U.S. Pat. Nos. 5,356,802; 5,436,150and 5,487,994; as well as Li et al. Proc., Natl. Acad. Sci. USA 89(1992):4275-4279; Li et al. Proc. Natl. Acad. Sci. USA, 90:2764-2768(1993); Kim et al. Proc. Natl. Acad. Sci. USA. 91:883-887 (1994a); Kimet al. J. Biol. Chem. 269:31, 978-31,982 (1994b). One or more of theseenzymes (or enzymatically functional fragments thereof) can be used as asource of cleavage domains.

The DNA-binding domain, which can, in principle, be designed to targetany genomic location of interest, can be a tandem array of Cys₂His₂ zincfingers, each of which generally recognizes three to four nucleotides inthe target DNA sequence. The Cys₂His₂ domain has a general structure:Phe (sometimes Tyr)-Cys-(2 to 4 amino acids)-Cys-(3 aminoacids)-Phe(sometimes Tyr)-(5 amino acids)-Leu-(2 amino acids)-His-(3amino acids)-His. By linking together multiple fingers (the numbervaries: three to six fingers have been used per monomer in publishedstudies), ZFN pairs can be designed to bind to genomic sequences 18-36nucleotides long.

Engineering methods include, but are not limited to, rational design andvarious types of empirical selection methods. Rational design includes,for example, using databases including triplet (or quadruplet)nucleotide sequences and individual zinc finger amino acid sequences, inwhich each triplet or quadruplet nucleotide sequence is associated withone or more amino acid sequences of zinc fingers which bind theparticular triplet or quadruplet sequence. See, for example, U.S. Pat.Nos. 6,140,081; 6,453,242; 6,534,261; 6,610,512; 6,746,838; 6,866,997;7,067,617; U.S. Published Application Nos. 2002/0165356; 2004/0197892;2007/0154989; 2007/0213269; and International Patent ApplicationPublication Nos. WO 98/53059 and WO 2003/016496.

Transcription Activator-Like Effector Nucleases

In some embodiments, the element that induces a single or a doublestrand break in the target cell's genome is a nucleic acid construct orconstructs encoding a transcription activator-like effector nuclease(TALEN). TALENs have an overall architecture similar to that of ZFNs,with the main difference that the DNA-binding domain comes from TALeffector proteins, transcription factors from plant pathogenic bacteria.The DNA-binding domain of a TALEN is a tandem array of amino acidrepeats, each about 34 residues long. The repeats are very similar toeach other; typically they differ principally at two positions (aminoacids 12 and 13, called the repeat variable diresidue, or RVD). Each RVDspecifies preferential binding to one of the four possible nucleotides,meaning that each TALEN repeat binds to a single base pair, though theNN RVD is known to bind adenines in addition to guanine. TAL effectorDNA binding is mechanistically less well understood than that ofzinc-finger proteins, but their seemingly simpler code could prove verybeneficial for engineered-nuclease design. TALENs also cleave as dimers,have relatively long target sequences (the shortest reported so farbinds 13 nucleotides per monomer) and appear to have less stringentrequirements than ZFNs for the length of the spacer between bindingsites. Monomeric and dimeric TALENs can include more than 10, more than14, more than 20, or more than 24 repeats.

Methods of engineering TAL to bind to specific nucleic acids aredescribed in Cermak, et al, Nucl. Acids Res. 1-11 (2011). US PublishedApplication No. 2011/0145940, which discloses TAL effectors and methodsof using them to modify DNA. Miller et al. Nature Biotechnol 29: 143(2011) reported making TALENs for site-specific nuclease architecture bylinking TAL truncation variants to the catalytic domain of Foklnuclease. The resulting TALENs were shown to induce gene modification inimmortalized human cells. General design principles for TALE bindingdomains can be found in, for example, WO 2011/072246.

2. Gene Altering Polynucleotides

The nuclease activity of the genome editing systems described hereincleave target DNA to produce single or double strand breaks in thetarget DNA. Double strand breaks can be repaired by the cell in one oftwo ways: non-homologous end joining, and homology-directed repair. Innon-homologous end joining (NHEJ), the double-strand breaks are repairedby direct ligation of the break ends to one another. As such, no newnucleic acid material is inserted into the site, although some nucleicacid material may be lost, resulting in a deletion. In homology-directedrepair, a donor polynucleotide with homology to the cleaved target DNAsequence is used as a template for repair of the cleaved target DNAsequence, resulting in the transfer of genetic information from a donorpolynucleotide to the target DNA. As such, new nucleic acid material canbe inserted/copied into the site.

Therefore, in some embodiments, the genome editing compositionoptionally includes a donor polynucleotide. The modifications of thetarget DNA due to NHEJ and/or homology-directed repair can be used toinduce gene correction, gene replacement, gene tagging, transgeneinsertion, nucleotide deletion, gene disruption, gene mutation, etc.

Accordingly, cleavage of DNA by the genome editing composition can beused to delete nucleic acid material from a target DNA sequence bycleaving the target DNA sequence and allowing the cell to repair thesequence in the absence of an exogenously provided donor polynucleotide.

Alternatively, if the genome editing composition includes a donorpolynucleotide sequence that includes at least a segment with homologyto the target DNA sequence, the methods can be used to add, i.e., insertor replace, nucleic acid material to a target DNA sequence (e.g., to“knock in” a nucleic acid that encodes for a protein, an siRNA, anmiRNA, etc.), to add a tag (e.g., 6xHis, a fluorescent protein (e.g., agreen fluorescent protein; a yellow fluorescent protein, etc.),hemagglutinin (HA), FLAG, etc.), to add a regulatory sequence to a gene(e.g., promoter, polyadenylation signal, internal ribosome entrysequence (IRES), 2A peptide, start codon, stop codon, splice signal,localization signal, etc.), to modify a nucleic acid sequence (e.g.,introduce a mutation), and the like. As such, the compositions can beused to modify DNA in a site-specific, i.e., “targeted”, way, forexample gene knock-out, gene knock-in, gene editing, gene tagging, etc.as used in, for example, gene therapy.

In applications in which it is desirable to insert a polynucleotidesequence into a target DNA sequence, a polynucleotide including a donorsequence to be inserted is also provided to the cell. By a “donorsequence” or “donor polynucleotide” or “donor oligonucleotide” it ismeant a nucleic acid sequence to be inserted at the cleavage site. Thedonor polynucleotide typically contains sufficient homology to a genomicsequence at the cleavage site, e.g., 70%, 80%, 85%, 90%, 95%, or 100%homology with the nucleotide sequences flanking the cleavage site, e.g.,within about 50 bases or less of the cleavage site, e.g., within about30 bases, within about 15 bases, within about 10 bases, within about 5bases, or immediately flanking the cleavage site, to supporthomology-directed repair between it and the genomic sequence to which itbears homology. The donor sequence is typically not identical to thegenomic sequence that it replaces. Rather, the donor sequence maycontain at least one or more single base changes, insertions, deletions,inversions or rearrangements with respect to the genomic sequence, solong as sufficient homology is present to support homology-directedrepair. In some embodiments, the donor sequence includes anon-homologous sequence flanked by two regions of homology, such thathomology-directed repair between the target DNA region and the twoflanking sequences results in insertion of the non-homologous sequenceat the target region.

b. Peptide and Protein Expression Constructs

In some embodiments, the active agent is a nucleic acid encoding aprotein or a polypeptide. Although discussed here in the context ofmRNA, it will be appreciated that the nucleic acid active agent canitself be an mRNA, or can be a DNA or other oligonucleotide encoding themRNA (or a functional nucleic acid as discussed above). As discussed inmore detail below, the nucleic acid active agents, including mRNA andfunctional nucleic acids, can be encoded by a nucleic acid that encodesthe RNA. The nucleic acid can be operably linked to an expressioncontrol sequence. In some embodiments, the nucleic acid is a vector,integration construct, etc., that enables expression of the RNA in acell.

The mRNA can be a mature mRNA or pre-mRNA. Thus in some embodiments, themRNA includes introns. The mRNA can be a naturally occurring genetranscript, for example, a human gene transcript. The mRNA can be anartificial sequence that is not normally expressed in a naturallyoccurring organism. An exemplary artificial sequence is one thatcontains portions of gene sequences that are ligated together to form anopen reading frame that encodes a fusion protein. The portions of thatare ligated together can be from a single organism or from more than oneorganism.

The mRNA can encode a polypeptide that provides a therapeutic orprophylactic effect to an organism or that can be used to diagnose adisease or disorder in an organism. For example, for treatment ofcancer, autoimmune disorders, parasitic, viral, bacterial, fungal orother infections, the polypeptide can be a ligand or receptor for cellsof the immune system, or can function to stimulate or inhibit the immunesystem of an organism. Typically, it is not desirable to have prolongedongoing stimulation of the immune system, nor necessary to producechanges which last after successful treatment, since this may thenelicit a new problem. For treatment of an autoimmune disorder, it may bedesirable to inhibit or suppress the immune system during a flare-up,but not long term, which could result in the patient becoming overlysensitive to an infection. Thus in some embodiments, delivery of mRNAfor transient expression of the protein (or functional nucleic acid) ispreferred to sustained expression by a vector or gene integration.

The mRNA can include a 5′ cap. A 5′ cap (also termed an RNA cap, an RNA7-methylguanosine cap or an RNA m7G cap) is a modified guaninenucleotide that has been added to the “front” or 5′ end of a eukaryoticmessenger RNA shortly after the start of transcription. The 5′ capconsists of a terminal group which is linked to the first transcribednucleotide. Its presence is critical for recognition by the ribosome andprotection from RNases. Cap addition is coupled to transcription, andoccurs co-transcriptionally, such that each influences the other.Shortly after the start of transcription, the 5′ end of the mRNA beingsynthesized is bound by a cap-synthesizing complex associated with RNApolymerase. This enzymatic complex catalyzes the chemical reactions thatare required for mRNA capping. Synthesis proceeds as a multi-stepbiochemical reaction. The capping moiety can be modified to modulatefunctionality of mRNA such as its stability or efficiency oftranslation. The 5′ cap may, for example, be m7G(5′)ppp(5′)G,m7G(5′)ppp(5′)A, G(5′)ppp(5′)G or G(5′)ppp(5′)A cap analogs, which areall commercially available. The 5′ cap can also be ananti-reverse-cap-analog (ARCA) (see, e.g., Stepinski, et al., RNA,7:1468-95 (2001)) or any other suitable analog. The 5′ cap is providedusing techniques known in the art and described herein (Cougot, et al.,Trends in Biochem. Sci., 29:436-444 (2001); Stepinski, et al., RNA,7:1468-95 (2001); Elango, et al., Biochim. Biophys. Res. Commun.,330:958-966 (2005)).

The mRNA can contain an internal ribosome entry site (IRES) sequence.The IRES sequence may be any viral, chromosomal or artificially designedsequence which initiates cap-independent ribosome binding to mRNA andfacilitates the initiation of translation.

The mRNA can include a 5′ untranslated region. The 5′ UTR is upsteamfrom the coding sequence. Within the 5′ UTR is a sequence that isrecognized by the ribosome which allows the ribosome to bind andinitiate translation. The mechanism of translation initiation differs inProkaryotes and Eukaryotes.

The mRNA includes an “open reading frame” or “ORF,” which is a series ofnucleotides that contains a sequence of bases that could potentiallyencode a polypeptide or protein. An open reading frame is locatedbetween the start-code sequence (initiation codon or start codon) andthe stop-codon sequence (termination codon). The ORF can be from anaturally occurring sequence from the genome of an organism.

The mRNA can include a 3′ untranslated region. The 3′ UTR is foundimmediately following the translation stop codon. The 3′ UTR plays animportant role in translation termination as well as posttranscriptional gene expression.

In some embodiments, the mRNA is polyadenylated. “Polyadenylation”refers to the covalent linkage of a polyadenylyl moiety, or its modifiedvariant, to a messenger RNA molecule. In eukaryotic organisms, mostmessenger RNA (mRNA) molecules are polyadenylated at the 3′ end. The 3′poly(A) tail is a long sequence of adenine nucleotides (often severalhundred) added to the pre-mRNA through the action of an enzyme,polyadenylate polymerase. In higher eukaryotes, the poly(A) tail isadded onto transcripts that contain a specific sequence, thepolyadenylation signal. The poly(A) tail and the protein bound to it aidin protecting mRNA from degradation by exonucleases. Polyadenylation isalso important for transcription termination, export of the mRNA fromthe nucleus, and translation. Polyadenylation occurs in the nucleusimmediately after transcription of DNA into RNA, but additionally canalso occur later in the cytoplasm. After transcription has beenterminated, the mRNA chain is cleaved through the action of anendonuclease complex associated with RNA polymerase. The cleavage siteis usually characterized by the presence of the base sequence AAUAAA(SEQ ID NO:12) near the cleavage site. After the mRNA has been cleaved,adenosine residues are added to the free 3′ end at the cleavage site.

RNA, including mRNA and RNA-based functional nucleic acids, can beprepared by in vitro transcription using, for example, a purified linearDNA template containing a promoter, ribonucleotide triphosphates, abuffer system that includes DTT and magnesium ions, and an appropriatephage RNA polymerase. The template can be a vector, PCR product,synthetic oligonucleotide, or cDNA.

3. Vectors

Nucleic acids, including constructs encoding mRNAs and functionalnucleic acids such as those described above, can be inserted intovectors for expression in cells. As used herein, a “vector” is areplicon, such as a plasmid, phage, virus or cosmid, into which anotherDNA segment may be inserted so as to bring about the replication of theinserted segment. Vectors can be expression vectors. An “expressionvector” is a vector that includes one or more expression controlsequences, and an “expression control sequence” is a DNA sequence thatcontrols and regulates the transcription and/or translation of anotherDNA sequence.

Nucleic acids in vectors can be operably linked to one or moreexpression control sequences. As used herein, “operably linked” meansincorporated into a genetic construct so that expression controlsequences effectively control expression of a coding sequence ofinterest. Examples of expression control sequences include promoters,enhancers, and transcription terminating regions. A promoter is anexpression control sequence composed of a region of a DNA molecule,typically within 100 nucleotides upstream of the point at whichtranscription starts (generally near the initiation site for RNApolymerase II). To bring a coding sequence under the control of apromoter, it is necessary to position the translation initiation site ofthe translational reading frame of the polypeptide between one and aboutfifty nucleotides downstream of the promoter. Enhancers provideexpression specificity in terms of time, location, and level. Unlikepromoters, enhancers can function when located at various distances fromthe transcription site. An enhancer also can be located downstream fromthe transcription initiation site. A coding sequence is “operablylinked” and “under the control” of expression control sequences in acell when RNA polymerase is able to transcribe the coding sequence intomRNA, which then can be translated into the protein encoded by thecoding sequence, or into a functional nucleic acids.

The vector can be a viral vector. Nucleic acid molecules encodingproteins or functional nucleic acids can be packaged into retrovirusvectors using packaging cell lines that produce replication-defectiveretroviruses, as is well-known in the art. Other virus vectors may alsobe used, including recombinant adenoviruses and vaccinia virus, whichcan be rendered non-replicating.

In some embodiments the nucleic acid is designed for integration intothe host cell's genome. Nucleic acids that are delivered to cells whichare to be integrated into the host cell genome, typically containintegration sequences. These sequences are often viral relatedsequences, particularly when viral based systems are used. Techniquesfor integration of genetic material into a host genome are also knownand include, for example, systems designed to promote homologousrecombination with the host genome. These systems typically rely onsequence flanking the nucleic acid to be expressed that has enoughhomology with a target sequence within the host cell genome thatrecombination between the vector nucleic acid and the target nucleicacid takes place, causing the delivered nucleic acid to be integratedinto the host genome. These systems and the methods necessary to promotehomologous recombination are known to those of skill in the art.

4. Nucleic Acid Composition

The nucleic acid cargos can be DNA or RNA nucleotides which typicallyinclude a heterocyclic base (nucleic acid base), a sugar moiety attachedto the heterocyclic base, and a phosphate moiety which esterifies ahydroxyl function of the sugar moiety. The principal naturally-occurringnucleotides comprise uracil, thymine, cytosine, adenine and guanine asthe heterocyclic bases, and ribose or deoxyribose sugar linked byphosphodiester bonds.

In some embodiments, the oligonucleotides are composed of nucleotideanalogs that have been chemically modified to improve stability,half-life, or specificity or affinity for a target receptor, relative toa DNA or RNA counterpart. The chemical modifications include chemicalmodification of nucleobases, sugar moieties, nucleotide linkages, orcombinations thereof. As used herein ‘modified nucleotide” or“chemically modified nucleotide” defines a nucleotide that has achemical modification of one or more of the heterocyclic base, sugarmoiety or phosphate moiety constituents. In some embodiments, the chargeof the modified nucleotide is reduced compared to DNA or RNAoligonucleotides of the same nucleobase sequence. For example, theoligonucleotide can have low negative charge, no charge, or positivecharge.

Typically, nucleoside analogs support bases capable of hydrogen bondingby Watson-Crick base pairing to standard polynucleotide bases, where theanalog backbone presents the bases in a manner to permit such hydrogenbonding in a sequence-specific fashion between the oligonucleotideanalog molecule and bases in a standard polynucleotide (e.g.,single-stranded RNA or single-stranded DNA). In some embodiments, theanalogs have a substantially uncharged, phosphorus containing backbone.

a. Heterocyclic Bases

The principal naturally-occurring nucleotides include uracil, thymine,cytosine, adenine and guanine as the heterocyclic bases. Theoligonucleotides can include chemical modifications to their nucleobaseconstituents. Chemical modifications of heterocyclic bases orheterocyclic base analogs may be effective to increase the bindingaffinity or stability in binding a target sequence. Chemically-modifiedheterocyclic bases include, but are not limited to, inosine,5-(1-propynyl) uracil (pU), 5-(1-propynyl) cytosine (pC),5-methylcytosine, 8-oxo-adenine, pseudocytosine, pseudoisocytosine, 5and 2-amino-5-(2′-deoxy-.beta.-D-ribofuranosyl)pyridine(2-aminopyridine), and various pyrrolo- and pyrazolopyrimidinederivatives.

b. Sugar Modifications

Oligonucleotides can also contain nucleotides with modified sugarmoieties or sugar moiety analogs. Sugar moiety modifications include,but are not limited to, 2′-O-aminoetoxy, 2′-O-amonioethyl (2′-OAE),2′-O-methoxy, 2′-O-methyl, 2-guanidoethyl (2′-OGE), 2′-O,4′-C-methylene(LNA), 2′-O-(methoxyethyl) (2′-OME) and 2′-O—(N-(methyl)acetamido)(2′-OMA). In some embodiments, the functional nucleic acid is amorpholino oligonucleotide. Morpholino oligonucleotides are typicallycomposed of two more morpholino monomers containing purine or pyrimidinebase-pairing moieties effective to bind, by base-specific hydrogenbonding, to a base in a polynucleotide, which are linked together byphosphorus-containing linkages, one to three atoms long, joining themorpholino nitrogen of one monomer to the 5′ exocyclic carbon of anadjacent monomer. The purine or pyrimidine base-pairing moiety istypically adenine, cytosine, guanine, uracil or thymine. The synthesis,structures, and binding characteristics of morpholino oligomers aredetailed in U.S. Pat. Nos. 5,698,685, 5,217,866, 5,142,047, 5,034,506,5,166,315, 5,521,063, and 5,506,337.

Important properties of the morpholino-based subunits typically include:the ability to be linked in a oligomeric form by stable, unchargedbackbone linkages; the ability to support a nucleotide base (e.g.adenine, cytosine, guanine, thymidine, uracil or inosine) such that thepolymer formed can hybridize with a complementary-base target nucleicacid, including target RNA, with high T, even with oligomers as short as10-14 bases; the ability of the oligomer to be actively transported intomammalian cells; and the ability of an oligomer:RNA heteroduplex toresist RNAse degradation.

In some embodiments, oligonucleotides employ morpholino-based subunitsbearing base-pairing moieties, joined by uncharged linkages, asdescribed above.

c. Internucleotide Linkages

Oligonucleotides connected by an internucleotide bond that refers to achemical linkage between two nucleoside moieties. Modifications to thephosphate backbone of DNA or RNA oligonucleotides may increase thebinding affinity or stability oligonucleotides, or reduce thesusceptibility of oligonucleotides nuclease digestion. Cationicmodifications, including, but not limited to, diethyl-ethylenediamide(DEED) or dimethyl-aminopropylamine (DMAP) may be especially useful dueto decrease electrostatic repulsion between the oligonucleotide and atarget. Modifications of the phosphate backbone may also include thesubstitution of a sulfur atom for one of the non-bridging oxygens in thephosphodiester linkage. This substitution creates a phosphorothioateinternucleoside linkage in place of the phosphodiester linkage.Oligonucleotides containing phosphorothioate internucleoside linkageshave been shown to be more stable in vivo.

Examples of modified nucleotides with reduced charge include modifiedinternucleotide linkages such as phosphate analogs having achiral anduncharged intersubunit linkages (e.g., Sterchak, E. P. et al., Organic.Chem., 52:4202, (1987)), and uncharged morpholino-based polymers havingachiral intersubunit linkages (see, e.g., U.S. Pat. No. 5,034,506), asdiscussed above. Some internucleotide linkage analogs includemorpholidate, acetal, and polyamide-linked heterocycles.

The oligonucleotides can be locked nucleic acids. Locked nucleic acids(LNA) are modified RNA nucleotides (see, for example, Braasch, et al.,Chem. Biol., 8(1):1-7 (2001)). LNAs form hybrids with DNA which are morestable than DNA/DNA hybrids, a property similar to that of peptidenucleic acid (PNA)/DNA hybrids. Therefore, LNA can be used just as PNAmolecules would be. LNA binding efficiency can be increased in someembodiments by adding positive charges to it. Commercial nucleic acidsynthesizers and standard phosphoramidite chemistry are used to makeLNAs.

In some embodiments, the oligonucleotides are composed of peptidenucleic acids. Peptide nucleic acids (PNAs) are synthetic DNA mimics inwhich the phosphate backbone of the oligonucleotide is replaced in itsentirety by repeating N-(2-aminoethyl)-glycine units and phosphodiesterbonds are typically replaced by peptide bonds. The various heterocyclicbases are linked to the backbone by methylene carbonyl bonds. PNAsmaintain spacing of heterocyclic bases that is similar to conventionalDNA oligonucleotides, but are achiral and neutrally charged molecules.Peptide nucleic acids are comprised of peptide nucleic acid monomers.

Other backbone modifications include peptide and amino acid variationsand modifications. Thus, the backbone constituents of oligonucleotidessuch as PNA may be peptide linkages, or alternatively, they may benon-peptide peptide linkages. Examples include acetyl caps, aminospacers such as 8-amino-3,6-dioxaoctanoic acid (referred to herein as0-linkers), amino acids such as lysine are particularly useful ifpositive charges are desired in the PNA, and the like. Methods for thechemical assembly of PNAs are well known. See, for example, U.S. Pat.Nos. 5,539,082, 5,527,675, 5,623,049, 5,714,331, 5,736,336, 5,773,571and 5,786,571.

Oligonucleotides optionally include one or more terminal residues ormodifications at either or both termini to increase stability, and/oraffinity of the oligonucleotide for its target. Commonly used positivelycharged moieties include the amino acids lysine and arginine, althoughother positively charged moieties may also be useful. Oligonucleotidesmay further be modified to be end capped to prevent degradation using apropylamine group. Procedures for 3′ or 5′ capping oligonucleotides arewell known in the art.

The functional nucleic acid can be single stranded or double stranded.

C. Tissue Targeting Ligands, Cell Adhesion Ligands, and Endosomal UptakeLigands 1. Targeting Moieties

The nanoparticles, cargo they contain, or a combination thereof canoptionally include a targeting moiety, i.e., a moiety able to bind to orotherwise associate with a biological entity, for example, a membranecomponent, a cell surface receptor, or a molecule. In one embodiment,the targeting moiety has a specificity (as measured via a disassociationconstant) of less than about 1 micromolar, at least about 10 micromolar,or at least about 100 micromolar. Numerous examples of targetingmoieties are known, some of which are more selective than others. Theligand can be selected based on the disease to be treated, the targetcells, tissue or organ, and the desired delivery strategy (e.g., into acells or into the extracellular space). The particles or cargo caninclude two, three, or more targeting moieties. In some embodiments,some polymers of the particle have a targeting moiety attached theretoand others do not. In this way, the density of the targeting moiety onthe surface of the particle can be manipulated.

The targeting signal can include a sequence of monomers that facilitatesin vivo localization of the molecule. The monomers can be amino acids,nucleotide or nucleoside bases, or sugar groups such as glucose,galactose, and the like which form carbohydrate targeting signals.Exemplary targeting molecules include small molecules, peptides,aptamers, polynucleotides, and antibodies and antigen binding fragmentsthereof. In certain embodiments, the antibody is polyclonal, monoclonal,linear, humanized, chimeric or a fragment thereof. Representativeantibody fragments are those fragments that bind the antibody bindingportion such as Fab, Fab′, F(ab′), Fv diabodies, linear antibodies,single chain antibodies and bispecific antibodies.

Targeting signals or sequences can be specific for a host, tissue,organ, cell, organelle, non-nuclear organelle, or cellular compartment.For example, in some embodiments the particle or a cargo thereofincludes a cell-specific targeting domain, an organelle specifictargeting domain to enhance delivery to a subcellular organelle, or acombination thereof. For example, the particle can include targetingmoiety that directs the particle to a microenvironment where the cargois released. A second targeting moiety on the cargo can then enhancedelivery to cargo into a target cell or cell(s) in the microenvironment.In some embodiment, the particle includes a moiety that targets it to atissue, cell or organ, and the cargo includes a moiety that enhancesdelivery of the cargo to a subcellular location such as an organelle.

General classes and methods of targeting are discussed here, andspecific exemplary cell, tissue, organ, and microenvironment specifictargets are discussed in more detail and the sections below devoted totherapeutic strategies and in the working Examples.

a. Cell Targeting

The particles, there cargo, or a combination thereof can be modified totarget a specific cell type or population of cells.

For example, the particles and cargo can be modified withgalactosyl-terminating macromolecules to target the polypeptide ofinterest to the liver or to liver cells. The modified particles andcargo selectively enters hepatocytes after interaction of the carriergalactose residues with the asialoglycoprotein receptor present in largeamounts and high affinity only on these cells.

In some embodiments, the targeting signal binds to its ligand orreceptor which is located on the surface of a target cell such as tobring the composition and cell membranes sufficiently close to eachother to allow penetration of the composition into the cell.

The targeting molecule can be, for example, an antibody or antigenbinding fragment thereof, an antibody domain, an antigen, a T-cellreceptor, a cell surface receptor, a cell surface adhesion molecule, amajor histocompatibility locus protein, a viral envelope protein and apeptide selected by phage display that binds specifically to a definedcell.

Targeting the particles or cargo to specific cells can be accomplishedby modifying the particle or cargo to express specific cell and tissuetargeting signals. These sequences target specific cells and tissues. Insome embodiments the interaction of the targeting signal with the celldoes not occur through a traditional receptor:ligand interaction. Theeukaryotic cell comprises a number of distinct cell surface molecules.The structure and function of each molecule can be specific to theorigin, expression, character and structure of the cell. Determining theunique cell surface complement of molecules of a specific cell type canbe determined using techniques well known in the art.

One skilled in the art will appreciate that the tropism of the particlesand cargo can be altered by changing the targeting signal. For example,the compositions can be modified to include cell surface antigenspecific antibodies. Exemplary cell surface antigens are disclosed inWagner et al., Adv Gen, 53:333-354 (2005). Tumor antigens discussed inmore detail below.

It is known in the art that nearly every cell type in a tissue in amammalian organism possesses some unique cell surface receptor orantigen. Thus, it is possible to incorporate nearly any ligand for thecell surface receptor or antigen as a targeting signal. For example,peptidyl hormones can be used a targeting moieties to target delivery tothose cells which possess receptors for such hormones. Chemokines andcytokines can similarly be employed as targeting signals to targetdelivery of the complex to their target cells. A variety of technologieshave been developed to identify genes that are preferentially expressedin certain cells or cell states and one of skill in the art can employsuch technology to identify targeting signals which are preferentiallyor uniquely expressed on the target tissue of interest

i. Brain Targeting

The targeting signal can be directed to cells of the nervous system,including the brain and peripheral nervous system. Cells in the braininclude several types and states and possess unique cell surfacemolecules specific for the type. Furthermore, cell types and states canbe further characterized and grouped by the presentation of common cellsurface molecules.

The targeting signal can be directed to specific neurotransmitterreceptors expressed on the surface of cells of the nervous system. Thedistribution of neurotransmitter receptors is well known in the art andone so skilled can direct the compositions described by usingneurotransmitter receptor specific antibodies as targeting signals.Furthermore, given the tropism of neurotransmitters for their receptors,in one embodiment the targeting signal consists of a neurotransmitter orligand capable of specifically binding to a neurotransmitter receptor.

The targeting signal can be specific to cells of the nervous systemwhich may include astrocytes, microglia, neurons, oligodendrites andSchwann cells. These cells can be further divided by their function,location, shape, neurotransmitter class and pathological state. Cells ofthe nervous system can also be identified by their state ofdifferentiation, for example stem cells. Exemplary markers specific forthese cell types and states are well known in the art and include, butare not limited to CD133 and Neurosphere.

ii. Muscle Targeting

The targeting signal can be directed to cells of the musculoskeletalsystem. Muscle cells include several types and possess unique cellsurface molecules specific for the type and state. Furthermore, celltypes and states can be further characterized and grouped by thepresentation of common cell surface molecules.

For example, the targeting signal can be directed to specificneurotransmitter receptors expressed on the surface of muscle cells. Thedistribution of neurotransmitter receptors is well known in the art andone so skilled can direct the compositions described by usingneurotransmitter receptor specific antibodies as targeting signals.Furthermore, given the tropism of neurotransmitters for their receptors,in some embodiments the targeting signal consists of a neurotransmitter.Exemplary neurotransmitters expressed on muscle cells that can betargeted include but are not limited to acetycholine and norepinephrine.

The targeting signal can be specific to muscle cells which consist oftwo major groupings, Type I and Type II. These cells can be furtherdivided by their function, location, shape, myoglobin content andpathological state. Muscle cells can also be identified by their stateof differentiation, for example muscle stem cells. Exemplary markersspecific for these cell types and states are well known in the artinclude, but are not limited to MyoD, Pax7 and MR4.

iii. Antibodies

Another embodiment provides an antibody or antigen binding fragmentthereof bound to the disclosed proteins of interest acting as thetargeting signal. The antibodies or antigen binding fragment thereof areuseful for directing the vector to a cell type or cell state. In oneembodiment, the polypeptide of interest possesses an antibody bindingdomain, for example from proteins known to bind antibodies such asProtein A and Protein G from Staphylococcus aureus.

In some embodiments, the targeting domain includes all or part of anantibody that directs the vector to the desired target cell type or cellstate. Antibodies can be monoclonal or polyclonal, but are preferablymonoclonal. For human gene therapy purposes, antibodies are derived fromhuman genes and are specific for cell surface markers, and are producedto reduce potential immunogenicity to a human host as is known in theart. For example, transgenic mice which contain the entire humanimmunoglobulin gene cluster are capable of producing “human” antibodiescan be utilized. In one embodiment, fragments of such human antibodiesare employed as targeting signals. In a preferred embodiment, singlechain antibodies modeled on human antibodies are prepared in prokaryoticculture.

In preferred embodiments the polypeptide of interest is itself a fusionprotein. The fusion protein can include, for example, apolynucleotide-binding polypeptide, a protein transduction domain, andoptionally one or more targeting signals. Other exemplary fusionproteins containing a mitochondrial transcription factor polypeptidethat are suitable for use as a polypeptide of interest are disclosed inU.S. Pat. Nos. 8,039,587, 8,062,891, 8,133,733.

b. Organelle Targeting

In some embodiments, the particle, cargo, or a combination thereof ismodified to target a subcellular organelle. Targeting of the disclosedcomposition to organelles can be accomplished by modifying thecomposition to contain specific organelle targeting signals. Thesesequences can target organelles, either specifically ornon-specifically. In some embodiments the interaction of the targetingsignal with the organelle does not occur through a traditionalreceptor:ligand interaction.

The eukaryotic cell comprises a number of discrete membrane boundcompartments, or organelles. The structure and function of eachorganelle is largely determined by its unique complement of constituentpolypeptides. However, the vast majority of these polypeptides begintheir synthesis in the cytoplasm. Thus organelle biogenesis and upkeeprequire that newly synthesized proteins can be accurately targeted totheir appropriate compartment. This is often accomplished byamino-terminal signaling sequences, as well as post-translationalmodifications and secondary structure.

Organelles can have single or multiple membranes and exist in both plantand animal cells. Depending on the function of the organelle, theorganelle can consist of specific components such as proteins andcofactors. The composition delivered to the organelle can enhance orinhibit to the functioning of the organelle. Exemplary organellesinclude the nucleus, mitochondrion, chloroplast, lysosome, peroxisome,Golgi, endoplasmic reticulum, and nucleolus. Some organelles, such asmitochondria and chloroplasts, contain their own genome. Nucleic acidsare replicated, transcribed, and translated within these organelles.Proteins are imported and metabolites are exported.

There can be an exchange of material across the membranes of organelles.Synthetic organelles can be formed from lipids and can contain specificproteins within the lipid membranes. Additionally, the content ofsynthetic organelles can be manipulated to contain components for thetranslation of nucleic acids.

In certain embodiments the particle, the cargo, or a combination thereofspecifically target mitochondria. Mitochondria contain the molecularmachinery for the conversion of energy from the breakdown of glucoseinto adenosine triphosphate (ATP). The energy stored in the high energyphosphate bonds of ATP is then available to power cellular functions.Cells with high metabolic activity, such as heart muscle, have many welldeveloped mitochondria.

Mitochondrial targeting agents can include a sequence of highlypositively charged amino acids. This allows the protein to be targetedto the highly negatively charged mitochondria. Unlike receptor:ligandapproaches that rely upon stochastic Brownian motion for the ligand toapproach the receptor, such targeting signals are drawn to mitochondriabecause of charge. Therefore, in some embodiments, the mitochondrialtargeting agent is a protein transduction domain including but notlimited to the protein transduction domains discussed in more detailbelow.

Mitochondrial targeting agents also include short peptide sequences(Yousif, et al., Chembiochem., 10(13):2131 (2009)), for example,mitochondrial transporters-synthetic cell-permeable peptides, also knownas mitochondria-penetrating peptides (MPPs), that are able to entermitochondria. MPPs are typically cationic, but also lipophilic; thiscombination of characteristics facilitates permeation of the hydrophobicmitochondrial membrane. For example, MPPs can include alternatingcationic and hydrophobic residues (Horton, et al., Chem Biol.,15(4):375-82 (2008)). Some MPPs include delocalized lipophilic cations(DLCs) in the peptide sequence instead of, or in addition to naturalcationic amino acids (Kelley, et al., Pharm. Res., 2011 Aug. 11 [Epubahead of print]). Other variants can be based on an oligomericcarbohydrate scaffold, for example attaching guanidinium moieties due totheir delocalized cationic form (Yousif, et al., Chembiochem.,10(13):2131 (2009).

Mitochondrial targeting agents also include mitochondrial localizationsignals or mitochondrial targeting signals. Many mitochondrial proteinsare synthesized as cytosolic precursor proteins containing a leadersequence, also known as a presequence, or peptide signal sequence. Manysequences are known in the art, see for example, U.S. Pat. No.8,039,587. The identification of the specific sequences necessary fortranslocation of a linked compound into a mitochondrion can bedetermined using predictive software known to those skilled in the art.

In some embodiments the target moiety directs the composition to thenucleus. Nuclear localization signals (NLS) or domains are known in theart and include for example, SV 40 T antigen or a fragment thereof. TheNLS can be simple cationic sequences of about 4 to about 8 amino acids,or can be bipartite having two interdependent positively chargedclusters separated by a mutation resistant linker region of about 10-12amino acids.

2. Endosomal Escape and Membrane Penetration

In some embodiments, the particles, cargo, or a combination thereofadditionally or alternatively include a moiety that enhances escape fromendosomes or macropinosomes. In some embodiments, particles enter cellsthrough endocytosis and are entrapped in endosomes. These earlyendosomes subsequently fuse with sorting endosomes, which in turntransfer their contents to the late endosomes. Late endosomal vesiclesare acidified (pH 5-6) by membrane-bound proton-pump ATPases. If theparticles are not released from the endosome, for example, by pH-induceddegradation and the associated “sponge” effect as discussed in moredetail below, the endosomal content can be relocated to the lysosomes,which are further acidified (pH ˜4.5) and contain various nucleases thatpromote the degradation of nucleic acids. To avoid lysosomal degradationof cargo, particularly nucleic acid cargo, the particle including thecargo, or the cargo itself (following release from the particle) escapesfrom the endosome into the cytosol. This is particularly preferred formRNA and functional nucleic acid cargos which may rely on cytosoliccellular machinery for their activity.

Strategies to promote endosomal release are known in the art, andinclude, for example, the use of fusogenic lipids, polymers with highbuffering capacity and membrane-interacting peptides (exemplarystrategies are reviewed in Dominska and Dykxhoorn, J Cell Sci, 123:1183-1189 (2010)). In particularly preferred embodiments, the endosomalescape sequence is a membrane interacting peptide. In some embodiments,the endosomal escape sequence is a protein transduction domain. Thus insome embodiments the endosomal escape sequence is part of, orconsecutive with, the protein transduction domain. In some embodiments,the endosomal escape sequence is non-consecutive with the proteintransduction domain or provided in the absence of a protein transductiondomain. In some embodiments the endosomal escape sequence includes aportion of the hemagglutinin peptide from influenza (HA).

Examples of endosomal escape sequences are known in the art. See, forexample, WO 2013/103972. Hatakeyama, et al., have described a fusogenicPEG-peptide-DOPE (PPD) construct and a pH-sensitive fusogenic GALApeptide (Hatakeyama, et al., J Control. Release 139, 127-132 (2009)) andthat PPD constructs can be cleaved by matrix metalloproteinases that arespecifically secreted by cancer cells, enhancing the delivery of siRNAcomplexed with this carrier to tumor cells (Hatakeyama, et al., GeneTher., 14, 68-77 (2007)).

Another membrane-destabilization mechanism takes advantage of thepore-forming ability of viroporins, highly hydrophobic proteins thatcreate channels and facilitate ion flow across biological membranes(Gonzalez and Carrasco, FEBS Lett. 552, 28-34 (2003)). For example,peptides derived from the endodomain of the HIV gp41 envelopeglycoprotein (sequence corresponding to residues 783-806 of gp160) formpores in the cell membrane by adopting an amphipathic α-helicalstructure (Costin et al., Virol. J., 4:123 (2007)) and (Kwon et al.,Bioconjugate Chem., 19, 920-927 (2008)).

The influenza-derived fusogenic peptide diINF-7 has also been shown toenhance endosomal release (Oliveira et al., Int. J. Pharm. 331, 211-214(2007)).

3. Protein Transduction Domains

The particles, any of the active agents, but particularly protein andnucleic acid agents, or a combination thereof can include a proteintransduction domain to improve delivery of the active agent acrossextracellular membranes, intracellular membranes, or the combinationthereof. As used herein, a “protein transduction domain” or PTD refersto a polypeptide, polynucleotide, carbohydrate, organic or inorganiccompound that facilitates traversing a lipid bilayer, micelle, cellmembrane, organelle membrane, or vesicle membrane. A PTD attached toanother molecule facilitates the molecule traversing membranes, forexample going from extracellular space to intracellular space, orcytosol to within an organelle.

The protein transduction domain can be a polypeptide. A proteintransduction domain can be a polypeptide including positively chargedamino acids. Thus, some embodiments include PTDs that are cationic oramphipathic. Protein transduction domains (PTD), also known as a cellpenetrating peptides (CPP), are typically polypeptides includingpositively charged amino acids. PTDs are known in the art, and includebut are not limited to small regions of proteins that are able to crossa cell membrane in a receptor-independent mechanism (Kabouridis, P.,Trends in Biotechnology (11):498-503 (2003)). Although several PTDs havebeen documented, the two most commonly employed PTDs are derived fromTAT (Frankel and Pabo, Cell, 55(6):1189-93(1988)) protein of HIV andAntennapedia transcription factor from Drosophila, whose PTD is known asPenetratin (Derossi et al., J Biol Chem., 269(14):10444-50 (1994)).Exemplary protein transduction domains include polypeptides with 11Arginine residues, or positively charged polypeptides or polynucleotideshaving 8-15 residues, preferably 9-11 residues. The Antennapediahomeodomain is 68 amino acid residues long and contains four alphahelices. See Derossi, JBC, 1994, 269, 10444) which provides Antppeptide. Oligoarginine is another preferred PTA (8 arginines) (Goun etal Bioconjugate Chem. 2006, 17, 787)). Penetratin is an active domain ofthis protein which consists of a 16 amino acid sequence derived from thethird helix of Antennapedia. TAT protein consists of 86 amino acids andis involved in the replication of HIV-1 (Vives, et al., JBC, 1997, 272,16010)) of the parent protein that appears to be critical for uptake.TAT has been favored for fusion to proteins of interest for cellularimport. Several modifications to TAT, including substitutions ofGlutamine to Alanine, i.e., Q>A, have demonstrated an increase incellular uptake anywhere from 90% (Wender et al., Proc Natl Acad SciUSA., 97(24):13003-8 (2000)) to up to 33 fold in mammalian cells. (Ho etal., Cancer Res., 61(2):474-7 (2001)).

4. Linkers

In different embodiments, the hydrophilic portion of the polymer can beconnected to the hydrophobic portion by a cleavable linker, thediagnostic, therapeutic or prophylactic agent may be connected to theamphiphilic polymer by a cleavable linker, and/or the targeting moietymay be connected to the amphiphilic polymer by a cleavable linker. Thelinker may be hydrolyzed by a chemical or enzymatic process. Preferably,the linker is cleaved by hydrogen peroxide, which is produced at sitesof inflammation or areas of high neutrophil concentration, therebyincreasing the selectivity of the nanoparticles. For example, the linkermay be hydrolyzed by a chemical or enzymatic process.

5. Exemplary Design Strategy

It will be appreciated that the stimuli-response particles and cargoeach optionally including targeting moiety, protein transductionmoieties, linkers, and other elements described herein are modular innature and can be utilized in various combinations as selected by theuser based on the intended use. Preferred uses and therapeuticstrategies include, but are not limited to, those described in moredetail below. Exemplary particles loaded with exemplary cargo andoptionally including exemplary targeting and membrane escape elementsare provided in, but not limited by the working Examples below. Forexample, in one non-limiting design strategy exemplified in Example 1,after encapsulating the agent(s) to be delivered, the resulting deliverysystem shows four unique features (FIG. 1C):

i) the surface-encoded iRGD peptide endows the NPs with tumor-targetingand tumor-penetrating abilities;

ii) the hydrophilic PEG shells prolong the blood circulation;

iii) a small population of cationic lipid-like grafts randomly dispersedin the hydrophobic poly(2-(diisopropylamino) ethylmethacrylate) (PDPA)segment can entrap siRNA in the hydrophobic cores of the NPs; and

iv) the rapid protonation of the ultra pH-responsive PDPA segmentinduces the endosomal swelling via the “proton sponge” effect, whichsynergizes with the insertion of the cationic lipid-like grafts intoendosomal membrane to induce membrane destabilization (Zhu X et al.,Proceedings of the National Academy of Sciences, 112, 7779-7784 (2015))and efficient endosomal escape.

III. Nanoparticle Formation

The nanoparticles are typically formed using an emulsion process, singleor double, using an aqueous and a non-aqueous solvent. Typically, thenanoparticles contain a minimal amount of the non-aqueous solvent aftersolvent removal. Preferred methods of preparing these nanoparticles aredescribed in the examples.

In one embodiment, nanoparticles are prepared using emulsion solventevaporation method. A polymeric material is dissolved in a waterimmiscible organic solvent and mixed with a drug solution or acombination of drug solutions. The water immiscible organic solvent ispreferably a GRAS ingredient such as chloroform, dichloromethane, andacyl acetate. The drug can be dissolved in, but is not limited to, oneor a plurality of the following: acetone, ethanol, methanol, isopropylalcohol, acetonitrile and Dimethyl sulfoxide (DMSO). An aqueous solutionis then added into the resulting mixture solution to yield emulsionsolution by emulsification. The emulsification technique can be, but notlimited to, probe sonication or homogenization through a homogenizer.

In another embodiment, nanoparticles are prepared usingnanoprecipitation methods or microfluidic devices. A polymeric materialis mixed with a drug or drug combinations in a water miscible organicsolvent. The water miscible organic solvent can be one or more of thefollowing: acetone, ethanol, methanol, isopropyl alcohol, acetonitrileand Dimethyl sulfoxide (DMSO). The resulting mixture solution is thenadded to an aqueous solution to yield nanoparticle solution. The agentsmay be associated with the surface of, encapsulated within, surroundedby, and/or distributed throughout the polymeric matrix of the particles.

In another embodiment, nanoparticles are prepared by the self-assemblyof the amphiphilic polymers, optionally including hydrophilic and/orhydrophobic polymers, using emulsion solvent evaporation, a single-stepnanoprecipitation method, or microfluidic devices.

Two methods to incorporate targeting moieties into the nanoparticlesinclude: i) conjugation of targeting ligands to the hydrophilic region(e.g. PEG) of polymers prior to nanoparticle preparation; and ii)incorporation of targeting molecules into nanoparticles where the PEGlayer on the nanoparticle surface can be cleaved in the presence of achemical or enzyme at tissues of interest to expose the targetingmolecules.

The diameters of the nanoparticles range between about 50 nm and about500 nm, preferably between about 50 nm and about 350 nm. In someembodiments, the diameters of the nanoparticles are about 100 nm. Thezeta potential of the nanoparticles ranges between about −50 mV andabout +50 mV, preferably between about −25 mV and +25 mV, mostpreferably between about −10 mV and about +10 my.

IV. Formulations and Methods of Administration A. Formulations

Formulations are prepared using a pharmaceutically acceptable “carrier”composed of materials that are considered safe and effective and may beadministered to an individual without causing undesirable biologicalside effects or unwanted interactions. The “carrier” is all componentspresent in the pharmaceutical formulation other than the activeingredient or ingredients. The term “carrier” includes but is notlimited to diluents, binders, lubricants, desintegrators, fillers, andcoating compositions.

Pharmaceutical compositions can be for administration by parenteral(intramuscular, intraperitoneal, intravenous (IV) or subcutaneousinjection), routes of administration and can be formulated in dosageforms appropriate for each route of administration. The compositions aremost typically administered systemically.

Compounds and pharmaceutical compositions thereof can be administered inan aqueous solution, by parenteral injection. The formulation may alsobe in the form of a suspension or emulsion. In general, pharmaceuticalcompositions are provided including effective amounts of the activeagent(s) and optionally include pharmaceutically acceptable diluents,preservatives, solubilizers, emulsifiers, adjuvants and/or carriers.Such compositions include diluents sterile water, buffered saline ofvarious buffer content (e.g., Tris-HCl, acetate, phosphate), pH andionic strength; and optionally, additives such as detergents andsolubilizing agents (e.g., TWEEN® 20, TWEEN® 80 also referred to aspolysorbate 20 or 80), anti-oxidants (e.g., ascorbic acid, sodiummetabisulfite), and preservatives. Examples of non-aqueous solvents orvehicles are propylene glycol, polyethylene glycol, vegetable oils, suchas olive oil and corn oil, gelatin, and injectable organic esters suchas ethyl oleate. The formulations may be lyophilized andredissolved/resuspended immediately before use. The formulation may besterilized by, for example, filtration through a bacteria retainingfilter, by incorporating sterilizing agents into the compositions, byirradiating the compositions, or by heating the compositions.

Preferably, the aqueous solution is water, physiologically acceptableaqueous solutions containing salts and/or buffers, such as phosphatebuffered saline (PBS), or any other aqueous solution acceptable foradministration to an animal or human. Such solutions are well known to aperson skilled in the art and include, but are not limited to, distilledwater, de-ionized water, pure or ultrapure water, saline,phosphate-buffered saline (PBS). Other suitable aqueous vehiclesinclude, but are not limited to, Ringer's solution and isotonic sodiumchloride. Aqueous suspensions may include suspending agents such ascellulose derivatives, sodium alginate, polyvinyl-pyrrolidone and gumtragacanth, and a wetting agent such as lecithin. Suitable preservativesfor aqueous suspensions include ethyl and n-propyl p-hydroxybenzoate.

An emulsion is a preparation of one liquid distributed in small globulesthroughout the body of a second liquid. The dispersed liquid is thediscontinuous phase, and the dispersion medium is the continuous phase.When oil is the dispersed liquid and an aqueous solution is thecontinuous phase, it is known as an oil-in-water emulsion, whereas whenwater or aqueous solution is the dispersed phase and oil or oleaginoussubstance is the continuous phase, it is known as a water-in-oilemulsion. The oil phase may consist at least in part of a propellant,such as an HFA propellant. Either or both of the oil phase and theaqueous phase may contain one or more surfactants, emulsifiers, emulsionstabilizers, buffers, and other excipients. Preferred excipients includesurfactants, especially non-ionic surfactants; emulsifying agents,especially emulsifying waxes; and liquid non-volatile non-aqueousmaterials, particularly glycols such as propylene glycol. The oil phasemay contain other oily pharmaceutically approved excipients. Forexample, materials such as hydroxylated castor oil or sesame oil may beused in the oil phase as surfactants or emulsifiers.

Buffers are used to control pH of a composition. Preferably, the buffersbuffer the composition from a pH of about 4 to a pH of about 7.5, morepreferably from a pH of about 4 to a pH of about 7, and most preferablyfrom a pH of about 5 to a pH of about 7.

Rapid escape and protection from the endosomal degradation can beenachieved by the inclusion of fusogenic lipids such as1,2-dioleoyl-sn-glycero-3-phosphoethanolamine (DOPE) in pH-sensitive andcationic liposome delivery systems. DOPE is a helper lipid capable ofdisrupting the endosomal membrane upon endosomal acidification by theformation of lipid hexagonal phases. Endosomal membrane disruption canrelease the DNA-based therapeutic and its delivery system into thecytoplasm. Lysosomatropic agents such as monensin and chloroquine, whichraise the endosomal pH, block acidification, and thus inhibit lysozymeactivity, have also been used to facilitate endosomal release of DNA.Endosomal degradation of DNA-based therapeutics can also be circumventedby the incorporation of viral peptides such as hemagglutinin HA2 andthose derived from adenoviruses in their delivery systems. HemagglutininHA2 undergoes conformational transition and leads to the destruction ofthe endosome, thereby facilitating the release of the DNA-basedtherapeutic. Enhanced rapid endosomal escape and enhanced transfectionhave also been achieved using fusogenic peptides such as poly(L-lysine)(PLL) and cationic polymers such as polyethylenimine (PEI) anddendrimers.

Active agent(s) and compositions thereof can be formulated for pulmonaryor mucosal administration. The administration can include delivery ofthe composition to the lungs, nasal, oral (sublingual, buccal), vaginal,or rectal mucosa. In a particular embodiment, the composition isformulated for and delivered to the subject sublingually.

In one embodiment, the compounds are formulated for pulmonary delivery,such as intranasal administration or oral inhalation. The respiratorytract is the structure involved in the exchange of gases between theatmosphere and the blood stream. The lungs are branching structuresultimately ending with the alveoli where the exchange of gases occurs.The alveolar surface area is the largest in the respiratory system andis where drug absorption occurs. The alveoli are covered by a thinepithelium without cilia or a mucus blanket and secrete surfactantphospholipids. The respiratory tract encompasses the upper airways,including the oropharynx and larynx, followed by the lower airways,which include the trachea followed by bifurcations into the bronchi andbronchioli. The upper and lower airways are called the conductingairways. The terminal bronchioli then divide into respiratorybronchiole, which then lead to the ultimate respiratory zone, thealveoli, or deep lung. The deep lung, or alveoli, is the primary targetof inhaled therapeutic aerosols for systemic drug delivery.

Pulmonary administration of therapeutic compositions comprised of lowmolecular weight drugs has been observed, for example, beta-androgenicantagonists to treat asthma. Other therapeutic agents that are active inthe lungs have been administered systemically and targeted via pulmonaryabsorption. Nasal delivery is useful for administration of therapeuticssince the nose has a large surface area available for drug absorptiondue to the coverage of the epithelial surface by numerous microvilli,the subepithelial layer is highly vascularized, the venous blood fromthe nose passes directly into the systemic circulation and thereforeavoids the loss of drug by first-pass metabolism in the liver, it offerslower doses, more rapid attainment of therapeutic blood levels, quickeronset of pharmacological activity, fewer side effects, high total bloodflow per cm³, porous endothelial basement membrane, and it is easilyaccessible.

The term aerosol as used herein refers to any preparation of a fine mistof particles, which can be in solution or a suspension, whether or notit is produced using a propellant. Aerosols can be produced usingstandard techniques, such as ultrasonication or high-pressure treatment.

Carriers for pulmonary formulations can be divided into those for drypowder formulations and for administration as solutions. Aerosols forthe delivery of therapeutic agents to the respiratory tract are known inthe art. For administration via the upper respiratory tract, theformulation can be formulated into a solution, e.g., water or isotonicsaline, buffered or un-buffered, or as a suspension, for intranasaladministration as drops or as a spray. Preferably, such solutions orsuspensions are isotonic relative to nasal secretions and of about thesame pH, ranging e.g., from about pH 4.0 to about pH 7.4 or, from pH 6.0to pH 7.0. Buffers should be physiologically compatible and include,simply by way of example, phosphate buffers. For example, arepresentative nasal decongestant is described as being buffered to a pHof about 6.2. One skilled in the art can readily determine a suitablesaline content and pH for an innocuous aqueous solution for nasal and/orupper respiratory administration.

B. Methods of Administration

Suitable parenteral administration routes include intravascularadministration (e.g., intravenous bolus injection, intravenous infusion,intra-arterial bolus injection, intra-arterial infusion and catheterinstillation into the vasculature); peri- and intra-tissue injection(e.g., intraocular injection, intra-retinal injection, or sub-retinalinjection); subcutaneous injection or deposition including subcutaneousinfusion (such as by osmotic pumps); direct application by a catheter orother placement device (e.g., an implant comprising a porous,non-porous, or gelatinous material).

The formulation can be administered in a single dose or in multipledoses. Certain factors may influence the dosage required to effectivelytreat a subject, including but not limited to the severity of thedisease or disorder, previous treatments, the general health and/or ageof the subject, and other diseases present. It will also be appreciatedthat the effective dosage of the oligonucleotide used for treatment mayincrease or decrease over the course of a particular treatment. Changesin dosage may result and become apparent from the results of diagnosticassays.

Dosing is dependent on severity and responsiveness of the diseasecondition to be treated, with the course of treatment lasting fromseveral days to several months, or until a cure is effected or adiminution of disease state is achieved. Optimal dosing schedules can becalculated from measurements of drug accumulation in the body of thepatient. Persons of ordinary skill can easily determine optimum dosages,dosing methodologies and repetition rates. Optimum dosages may varydepending on the relative potency of individual polynucleotides, and cangenerally be estimated based on EC50s found to be effective in vitro andin vivo animal models.

Dosage levels on the order of about 1 mg/kg to 100 mg/kg of body weightper administration are useful in the treatment of a disease. One skilledin the art can also readily determine an appropriate dosage regimen foradministering the disclosed polynucleotides to a given subject. Forexample, the formulation can be administered to the subject once, e.g.,as a single injection, infusion or bolus. Alternatively, the formulationcan be administered once or twice daily to a subject for a period offrom about three to about twenty-eight days, or from about seven toabout ten days.

V. Biomedical Applications and Therapeutic Strategies

Biomedical application of nanoparticles has introduced excitingopportunities for the improvement of disease diagnosis and treatment.Stimuli-responsive nanoparticles, which can undergo shape, structure andproperty change upon encountering endogenous or exogenous stimuli, canbe used in diverse range of biomedical applications, such as drugcontrolled release, nucleic acid delivery, imaging, and diagnostics. Thestimuli-responsive characteristic provides spatiotemporal control overthe macroscopic properties of the nanoparticles, and thus the release ofthe encapsulated cargo can occur directly at the desired site,minimizing toxic and side effects in surrounding, healthy tissue.Dissociation of the particle and release of its cargo, can be driven by,for example, pH-, redox-, light-, temperature-, enzyme-, orultrasound-responsive polymers composing the particles.

The stimuli that drive a response by the particle can be present withina cell (e.g., intracellularly) or outside cells in the extracellularmicroenvironment, or can be an external stimuli for example, light,heat, ultrasound, etc., which can be applied by the user to the targetsite. The particles can optionally include a targeting moiety or ligand.For embodiments in which intracellular release is desired, the targetingmoiety or ligand is typically one that preferentially binds to thesurface of a target cell and induces or allows the particle to beabsorbed or internalized by, for example, endocytosis ormicropinocytosis (Vranic et al., Particle and Fibre Toxicology,10(2):(12 page) (2013)). For embodiments in which extracellular releaseis desired, the targeting moiety or ligand can be one thatpreferentially binds to an extracellular target in the desiredmicroenvironment.

A. Exemplary Environments for Selective Delivery 1. Acidic Environment

pH responsive nanoparticles can be used to target tissues with acidicextracellular pH. Although the nanoparticles can optionally include acell, tissue, organ, or extracellular matrix-specific targeting moietyor ligand, a targeting moiety or ligand is not requirement. The pHresponsive nanoparticles can be designed to have spherical morphology ata pH above pKa to protect cargo during systemic circulation andinfiltration into tissues with extracellular pH at or around neutral orphysiological pH. The particles can dissociate at a pH below pKa,releasing its cargo into the microenvironment. In this way, theparticles selectively release their cargo at the target site.

pH responsive nanoparticles can also be used to deliver cargo intocells. Particles, preferable with a targeting moiety or ligand, can bindto a target cell and be absorbed or internalized. Upon encountering anacidic intracellular environment such as that of endosomes, the pHresponsive particles can dissociate and release their cargo. Theparticles can also optionally include a moiety that enhances endosomalescape, such as oligoarginine. As illustrated in the working Examplesbelow, particle dissociation within the endosome is believe to induceswelling of the endosome via “sponge” effect, thus achieving fast andhigh efficacy delivery of their cargo into the cytosol. Using anintracellular endosomal-release strategy, virtually any cell withendosomes (or another equivalently acidic intracellular environment,compartment, or organelle) can be the target cell. The addition of atargeting moiety can be used to accomplish selective delivery of theparticle into target cells over non-target cells. pH responsiveintracellular release can be most effective when the extracellular pHdoes not induce nanoparticle dissociation thus allowing the particles toabsorbed or internalized by cells.

In some embodiments, cargo is released below physiological pH (e.g.,7.4, or 7.2), or below neutral pH (e.g., 7.0), or in a pH range of about5.8 to about 7.3, or about 5.8 to about 6.9, or about 6.0 to about 6.5,or about 6.5 to about 6.9.

2. Temperature

In embodiments, cargo release is driven by a change in temperature. Inthe biomedical setting, a change in temperature will can be an increaseor decrease from the physiological temperature of the subject beingtreated. Normal human body temperature, also referred to as normothermiaor euthermia, depends upon the place in the body at which themeasurement is made, the time of day, as well as the activity level ofthe person. Typically values for oral measurement (under the tongue) are36.8±0.4° C. (98.2±0.72° F.) and internal (rectal, vaginal) measurementare 37.0° C. (98.6° F.) (Harrison's Principles of Internal Medicine,18e, Longo, Editor, Fauci, et al., Editor, Kasper). Human temperatureclassifications can be, for example, Hypothermia <35.0° C. (95.0° F.);Normal 36.5-37.5° C. (97.7-99.5° F.), Fever >37.5 or 38.3° C. (99.5 or100.9° F.), Hyperthermia >37.5 or 38.3° C. (99.5 or 100.9° F.),Hyperpyrexia >40.0 or 41.5° C. (104.0 or 106.7° F.). The particles canbe designed for release within one or more of these temperatureclassifications, or a sub-range thereof. It will be appreciated that asubject's normal body temperature can fluctuate, for example, with thetime of day, sleep vs. wake, eating vs. fasting, exercise, the amount ofclothing being worn, the ambient temperature, the anxiety or excitementlevel of the subject, etc., as is known in the art. The particles can betuned for release when body temperature drops below or exceeds apredetermined threshold, and therefore selectively release cargo duringcertain times of the day or night, caloric intake (or lack thereof),during exercise, anxiety, etc. The release can be local so systemic.

In addition of more global changes in overall body temperature, such asthose introduced above, the particles can be tuned for release at sitesof local temperature changes. For example, local, tissue-specificincrease in tissue temperature can occur at sites of inflammation,injury, infection, and cancer (e.g., tumor) (Chapter Nine, Inflammation,Tissue Repair, and Fever, pages 150-167). The change in temperature canbe relative to unaffected tissue and may occur in the presence orabsence of a global change in body temperature.

3. Reduction-Oxidation (Redox)

The release of nanoparticle cargo can be induced by areduction-oxidation (“redox”) reaction. In some embodiments, thepolymers composing the particles include one or more disulfide bonds.The particles can release their cargo when disulfide bond is reducedupon exposure to a reducing agent. In some embodiments, the reducingagent is a glutathione. L-Glutathione (GSH) is a tripeptide moleculethat can also act as an antioxidant. In cells, GSH reduces the disulfidebonds formed within cytoplasmic proteins to cysteines and reacts toother oxidized GSH to an oxidized form of glutathione disulfide (GSSG),also called L(−)-glutathione (Traverso, et al., Oxidative Medicine andCellular Longevity, Volume 2013 (2013), Article ID 972913, 10 pages). Asdiscussed in more detail below, intracellular levels of glutathione(GSH) are 100-1000 fold higher in cancer cells than in normal tissue,and thus redox-sensitive particles can be used to selective releasecargo in cells with higher-than-normal GSH, such as cancer cells. Forexample, one study showed that intracellular GHS levels in normal lungcells were about 11.20±0.58 (SEM) nmol GSH/mg protein (24 patients) witha range from 6.1 to 17.5 nmol GSH/mg protein, while GHS level inadenocarcinomas was 8.83±0.96 nmol/mg protein (8 patients); large cellcarcinomas was 8.25±2.51 nmol/mg protein (3 patients); and squamous cellcarcinomas 23.25±5.99 nmol/mg protein (8 patients) (Cook, et al., CancerResearch, 51:4287-4294 (1991).

The Examples below show that cargo can be released redox-sensitiveparticles in matter of minutes in the presences of 10 nM GSH.

In some embodiments, the reducing agent is not endogenous to the cell,tissue, organ, or other microenvironment. For example, in someembodiments, the reducing agent is administered locally or systemicallyto trigger release of the cargo from the particles in a local orsystemic fashion.

In addition to GSH, other reducing agents can also induce release of thecargo, however, it will be appreciated that in some embodiments, theuse, or the amount that can be used, of certain reducing agents islimited in biological and therapeutic applications by their toxicity.

4. External Stimuli

As introduced above, release of nanoparticle cargo can be induced byexternal stimuli, such as light, temperature, or ultrasound. The stimulican be applied globally, for example to the entire subject, orpreferably to a more limited or local aspect thereof. For example,light, heat (or cold), or ultrasound can be administered to a specifictissue(s), location(s), or combination thereof to modulate selectiverelease of cargo from particles accumulating or passing through thetargeted tissue or location. For example, heat (or cold) can be appliedto the target tissue or location to cause a local temperature shift thatinduces dissociation of the particle and release of its cargo. Radiationat different frequencies along the electromagnetic spectrum can also beused to release cargo. For example, particles can be formed that aresensitive to ionizing radiation, visible light, microwaves, orradiowaves. In particular embodiments, the particles are sensitive tovisible light (e.g., near ultraviolet, near infrared, mid infrared, farinfrared). Particles can also be formed that are sensitive to soundwaves. For example, in particular embodiments, the particles releasecargo in response to ultrasound.

In particular embodiments, the particles are sensitive to ultravioletlight. Ultraviolet (UV) light is an electromagnetic radiation with awavelength shorter than that of visible light but longer than X-rays.The wavelength of UV light is typically from about 400 nm (750 THz) toabout 10 nm (30 PHz). UV radiation can be divided into five categories:UV-A is about 320-400 nm, UV-B is 290-320 nm, UV-C is 220-209 nm, Far UVis 190-220 nm, and vacuum UV 40-190 nm. In some embodiments, theparticles are sensitive to UV-A, UV-B, UV-C, or a combination thereof.The Examples below illustrate that particles can be formed that therelease their cargo after exposure to UV light, for example 365 nm UVlight (16 W), for different time periods. In some embodiments, thesource provides a specific desired wavelength. In some embodiments, thesource provides a range of wavelength.

The external stimuli can be provided by the practitioner using, forexample, a piece of equipment that provides the stimuli. The stimuli canalso be provided by the environment and may or may not be under thecontrol of practitioner or user. For example, the sun generates visiblelight, heat, and UV radiation. Thus, in some embodiments, the particlesare designed to release their cargo in response to the sun.

Exposure to external stimuli can be carried out over minutes, hours,days or weeks. In some embodiments, the exposure is between about 1 andabout 120 minutes, for example, 10, 15, 30, 45, 60, 90, or 120 minutes.In some embodiments, the exposure is between about 1 and 48 hours, forexample, 1, 2, 3, 4, 5, 10, 12.5, 15, 20, 24, 36, or 48 hours. In someembodiments, the exposure is over two or more days.

B. Preferred Tissues to Target and Therapeutic Strategies

As discussed above, the particles can be used to selectively targetcells, tissues, organs, or microenvironments thereof. The selectiverelease of cargo at a target site can be used in strategies to treat avariety of diseases and disorders. Suitable methods can includeadministering a subject an effective amount of nanoparticles containinga therapeutic cargo to reduce or alleviate one or more symptoms of thedisease or disorder to be treated. The disclosed strategies can includetargeting certain intracellular and/or extracellular environments forselective release based on response-inducing stimuli alone, or incombination with one or more targeting moieties that enhance delivery toa desired cell type, tissue, organ, microenvironment, subcellularorganelle, or a combination thereof 1. Tumor targeting Methods oftreating cancer are provided. The nanoparticles can be designed, forexample, for release in the tumor microenvironment or within a tumorcells, or in an immune response microenvironment or within an immunecell. Suitable methods can include administering a subject an effectiveamount of nanoparticles containing a therapeutic cargo to reduce oralleviate one or more symptoms of the cancer. The effect of theparticles on the cancer can be direct or indirect. The compositions andmethods described herein are useful for treating subjects having benignor malignant tumors by delaying or inhibiting the growth of a tumor in asubject, reducing the growth or size of the tumor, inhibiting orreducing metastasis of the tumor, and/or inhibiting or reducing symptomsassociated with tumor development or growth.

The tumor microenvironment is the cellular environment in which thetumor exists, and can include surrounding blood vessels, immune cells,fibroblasts, bone marrow-derived inflammatory cells, lymphocytes,signaling molecules, and the extracellular matrix (ECM). The tumor andthe surrounding microenvironment are closely related and interactconstantly. Tumors can modulate the microenvironment by releasingextracellular signals, promoting tumor angiogenesis and inducingperipheral immune tolerance, while the immune cells in themicroenvironment can affect the growth and evolution of cancerous cells.The microenvironment in tumor tissue is different from the normaltissues. Thus, in some embodiments, the stimuli-responsive polymers aredesign to trigger the structural changes in reponse to stimuli that isunique to the tumor microenvironment including but not limited totemperature, pH, ionic strength, composition/organization of theextracellular matrix (ECM), over-expressed molecules or enzymes, andhypoxia.

Compared to normal tissues, the pH in tumor tissue is more acidic, thetissue temperature is relatively higher, oxygen concentrations arereduced (hypoxia), and some specific enzymes or chemicals areover-expressed. Hypoxia is an important characteristic of the tumormicroenvironment commonly found in cancers and a selection force for theglycolytic phenotype. Thus, in some embodiments, hypoxia-responsivestimula are used to selectively delivery cargo to an acidic tumormicroenvironment. For example, a hydrophobically modified2-nitroimidazole derivative conjugated to the backbone of thecarboxymethyl dextran described to target hypoxia (Thambi T et al.,Biomaterials. 2014 February; 35(5):1735-43) can be used with thenanoparticles.

The interstitial fluid of tumors and abscesses also has shown pH valuesof less than 6.0, averaging 0.2-0.6 units lower than mean extracellularpH of normal tissues (Kraus and Wolf, Tumour Biol, 17,133-154 (1996)).Tumors commonly have an extracellular environment with a pH in the rangeof, for example, 6.5-6.9. See, for example, Balkwill, et al., Journal ofCell Science, 125(23):5591-6 (2012) and Kato, et al., Cancer CellInternational, 13(89) (8 pages) (2013). Thus, in some embodiments,pH-sensitive nanoparticles are used to selectively deliver cargo to anacidic tumor microenvironment.

Tumors can also have elevated temperatures relative to the surround orotherwise normal or non-malignant tissue (see, e.g., Stefanadis, JCO,19(3):676-681 (2001)). Therefore, temperature-responsive particles canalso be utilized to selectively target tumors.

The intracellular levels of glutathione (GSH) are 100-1000 fold higherin cancer cells than in normal tissue. Redox-sensitive approach isparticularly promising to enhance the exposure of cancer cells totherapeutic molecules. Thus, in some embodiments, redox-responsiveparticles can also be utilized for delivering cargo to tumor cells.

a. Tumor Targeting Moieties

In addition or alternative to selectively targeting cancer cells bytargeting an acidic microenvironment, or one with an elevatedtemperature, cancer cells or their microenvironment can be specificallytargeted relative to healthy or normal cells by including a targetingmoiety. Tumor or tumor-associated neovasculature targeting domains canbe ligands that bind to cell surface antigens or receptors that arespecifically expressed on tumor cells or tumor-associated neovasculatureor microenvironment, or are overexpressed on tumor cells ortumor-associated neovasculature or microenvironment as compared tonormal tissue. Tumors also secrete a large number of ligands into thetumor microenvironment that affect tumor growth and development.Receptors that bind to ligands secreted by tumors, including, but notlimited to growth factors, cytokines and chemokines, including thechemokines provided below, can also be used. Ligands secreted by tumorscan be targeted using soluble fragments of receptors that bind to thesecreted ligands. Soluble receptor fragments are fragments polypeptidesthat may be shed, secreted or otherwise extracted from the producingcells and include the entire extracellular domain, or fragments thereof.In some embodiments, the targeting moiety is an antibody, for example asingle chain antibody, the binds to the target.

i. Cancer Antigens

Cancer antigens that can be targeted are well known in the art. Theantigen expressed by the tumor may be specific to the tumor, or may beexpressed at a higher level on the tumor cells as compared to non-tumorcells. Antigenic markers such as serologically defined markers known astumor associated antigens, which are either uniquely expressed by cancercells or are present at markedly higher levels (e.g., elevated in astatistically significant manner) in subjects having a malignantcondition relative to appropriate controls, are contemplated for use incertain embodiments.

Tumor-associated antigens may include, for example, cellularoncogene-encoded products or aberrantly expressed proto-oncogene-encodedproducts (e.g., products encoded by the neu, ras, trk, and kit genes),or mutated forms of growth factor receptor or receptor-like cell surfacemolecules (e.g., surface receptor encoded by the c-erb B gene). Othertumor-associated antigens include molecules that may be directlyinvolved in transformation events, or molecules that may not be directlyinvolved in oncogenic transformation events but are expressed by tumorcells (e.g., carcinoembryonic antigen, CA-125, melonoma associatedantigens, etc.) (see, e.g., U.S. Pat. No. 6,699,475; Jager, et al., Int.J. Cancer, 106:817-20 (2003); Kennedy, et al., Int. Rev. Immunol.,22:141-72 (2003); Scanlan, et al. Cancer Immun., 4:1 (2004)).

Genes that encode cellular tumor associated antigens include cellularoncogenes and proto-oncogenes that are aberrantly expressed. In general,cellular oncogenes encode products that are directly relevant to thetransformation of the cell, and because of this, these antigens areparticularly preferred targets for anticancer therapy. An example is thetumorigenic neu gene that encodes a cell surface molecule involved inoncogenic transformation. Other examples include the ras, kit, and trkgenes. The products of proto-oncogenes (the normal genes which aremutated to form oncogenes) may be aberrantly expressed (e.g.,overexpressed), and this aberrant expression can be related to cellulartransformation. Thus, the product encoded by proto-oncogenes can betargeted. Some oncogenes encode growth factor receptor molecules orgrowth factor receptor-like molecules that are expressed on the tumorcell surface. An example is the cell surface receptor encoded by thec-erbB gene. Other tumor-associated antigens may or may not be directlyinvolved in malignant transformation. These antigens, however, areexpressed by certain tumor cells and may therefore provide effectivetargets. Some examples are carcinoembryonic antigen (CEA), CA 125(associated with ovarian carcinoma), and melanoma specific antigens.

In ovarian and other carcinomas, for example, tumor associated antigensare detectable in samples of readily obtained biological fluids such asserum or mucosal secretions. One such marker is CA125, a carcinomaassociated antigen that is also shed into the bloodstream, where it isdetectable in serum (e.g., Bast, et al., N. Eng. J. Med., 309:883(1983); Lloyd, et al., Int. J. Canc., 71:842 (1997). CA125 levels inserum and other biological fluids have been measured along with levelsof other markers, for example, carcinoembryonic antigen (CEA), squamouscell carcinoma antigen (SCC), tissue polypeptide specific antigen (TPS),sialyl TN mucin (STN), and placental alkaline phosphatase (PLAP), inefforts to provide diagnostic and/or prognostic profiles of ovarian andother carcinomas (e.g., Sarandakou, et al., Acta Oncol., 36:755 (1997);Sarandakou, et al., Eur. J. Gynaecol. Oncol., 19:73 (1998); Meier, etal., Anticancer Res., 17(4B):2945 (1997); Kudoh, et al., Gynecol.Obstet. Invest., 47:52 (1999)). Elevated serum CA125 may also accompanyneuroblastoma (e.g., Hirokawa, et al., Surg. Today, 28:349 (1998), whileelevated CEA and SCC, among others, may accompany colorectal cancer(Gebauer, et al., Anticancer Res., 17(4B):2939 (1997)).

The tumor associated antigen, mesothelin, defined by reactivity withmonoclonal antibody K-1, is present on a majority of squamous cellcarcinomas including epithelial ovarian, cervical, and esophagealtumors, and on mesotheliomas (Chang, et al., Cancer Res., 52:181 (1992);Chang, et al., Int. J. Cancer, 50:373 (1992); Chang, et al., Int. J.Cancer, 51:548 (1992); Chang, et al., Proc. Natl. Acad. Sci. USA, 93:136(1996); Chowdhury, et al., Proc. Natl. Acad. Sci. USA, 95:669 (1998)).Using MAb K-1, mesothelin is detectable only as a cell-associated tumormarker and has not been found in soluble form in serum from ovariancancer patients, or in medium conditioned by OVCAR-3 cells (Chang, etal., Int. J. Cancer, 50:373 (1992)). Structurally related humanmesothelin polypeptides, however, also include tumor-associated antigenpolypeptides such as the distinct mesothelin related antigen (MRA)polypeptide, which is detectable as a naturally occurring solubleantigen in biological fluids from patients having malignancies (see WO00/50900).

A tumor antigen may include a cell surface molecule. Tumor antigens ofknown structure and having a known or described function, include thefollowing cell surface receptors: HER1 (GenBank Accession No. U48722),HER2 (Yoshino, et al., J. Immunol., 152:2393 (1994); Disis, et al.,Canc. Res., 54:16 (1994); GenBank Acc. Nos. X03363 and M17730), HER3(GenBank Acc. Nos. U29339 and M34309), HER4 (Plowman, et al., Nature,366:473 (1993); GenBank Acc. Nos. L07868 and T64105), epidermal growthfactor receptor (EGFR) (GenBank Acc. Nos. U48722, and KO3193), vascularendothelial cell growth factor (GenBank No. M32977), vascularendothelial cell growth factor receptor (GenBank Acc. Nos. AF022375,1680143, U48801 and X62568), insulin-like growth factor-I (GenBank Acc.Nos. X00173, X56774, X56773, X06043, European Patent No. GB 2241703),insulin-like growth factor-II (GenBank Acc. Nos. X03562, X00910, M17863and M17862), transferrin receptor (Trowbridge and Omary, Proc. Nat.Acad. USA, 78:3039 (1981); GenBank Acc. Nos. X01060 and M11507),estrogen receptor (GenBank Acc. Nos. M38651, X03635, X99101, U47678 andM12674), progesterone receptor (GenBank Acc. Nos. X51730, X69068 andM15716), follicle stimulating hormone receptor (FSH—R) (GenBank Acc.Nos. Z34260 and M65085), retinoic acid receptor (GenBank Acc. Nos.L12060, M60909, X77664, X57280, X07282 and X06538), MUC-1 (Barnes, etal., Proc. Nat. Acad. Sci. USA, 86:7159 (1989); GenBank Acc. Nos. M65132and M64928) NY-ESO-1 (GenBank Acc. Nos. AJ003149 and U87459), NA 17-A(PCT Publication No. WO 96/40039), Melan-A/MART-1 (Kawakami, et al.,Proc. Nat. Acad. Sci. USA, 91:3515 (1994); GenBank Acc. Nos. U06654 andU06452), tyrosinase (Topalian, et al., Proc. Nat. Acad. Sci. USA,91:9461 (1994); GenBank Acc. No. M26729; Weber, et al., J. Clin. Invest,102:1258 (1998)), Gp-100 (Kawakami, et al., Proc. Nat. Acad. Sci. USA,91:3515 (1994); GenBank Acc. No. 573003, Adema, et al., J. Biol. Chem.,269:20126 (1994)), MAGE (van den Bruggen, et al., Science, 254:1643(1991)); GenBank Acc. Nos. U93163, AF064589, U66083, D32077, D32076,D32075, U10694, U10693, U10691, U10690, U10689, U10688, U10687, U10686,U10685, L18877, U10340, U10339, L18920, U03735 and M77481), BAGE(GenBank Acc. No. U19180; U.S. Pat. Nos. 5,683,886 and 5,571,711), GAGE(GenBank Acc. Nos. AF055475, AF055474, AF055473, U19147, U19146, U19145,U19144, U19143 and U19142), any of the CTA class of receptors includingin particular HOM-MEL-40 antigen encoded by the SSX2 gene (GenBank Acc.Nos. X86175, U90842, U90841 and X86174), carcinoembryonic antigen (CEA,Gold and Freedman, J. Exp. Med., 121:439 (1985); GenBank Acc. Nos.M59710, M59255 and M29540), and PyLT (GenBank Acc. Nos. J02289 andJ02038); p97 (melanotransferrin) (Brown, et al., J. Immunol., 127:539-46(1981); Rose, et al., Proc. Natl. Acad. Sci. USA, 83:1261-61 (1986)).

Additional tumor associated antigens include prostate surface antigen(PSA) (U.S. Pat. Nos. 6,677,157; 6,673,545); β-human chorionicgonadotropin β-HCG) (McManus, et al., Cancer Res., 36:3476-81 (1976);Yoshimura, et al., Cancer, 73:2745-52 (1994); Yamaguchi, et al., Br. J.Cancer, 60:382-84 (1989): Alfthan, et al., Cancer Res., 52:4628-33(1992)); glycosyltransferase β-1,4-N-acetylgalactosaminyltransferases(GalNAc) (Hoon, et al., Int. J. Cancer, 43:857-62 (1989); Ando, et al.,Int. J. Cancer, 40:12-17 (1987); Tsuchida, et al., J. Natl. Cancer,78:45-54 (1987); Tsuchida, et al., J. Natl. Cancer, 78:55-60 (1987));NUC18 (Lehmann, et al., Proc. Natl. Acad. Sci. USA, 86:9891-95 (1989);Lehmann, et al., Cancer Res., 47:841-45 (1987)); melanoma antigen gp75(Vijayasardahi, et al., J. Exp. Med., 171:1375-80 (1990); GenBankAccession No. X51455); human cytokeratin 8; high molecular weightmelanoma antigen (Natali, et al., Cancer, 59:55-63 (1987); keratin 19(Datta, et al., J. Clin. Oncol., 12:475-82 (1994)).

Tumor antigens of interest include antigens regarded in the art as“cancer/testis” (CT) antigens that are immunogenic in subjects having amalignant condition (Scanlan, et al., Cancer Immun., 4:1 (2004)). CTantigens include at least 19 different families of antigens that containone or more members and that are capable of inducing an immune response,including but not limited to MAGEA (CT1); BAGE (CT2); MAGEB (CT3); GAGE(CT4); SSX (CT5); NY-ESO-1 (CT6); MAGEC (CT7); SYCP1 (C8); SPANXB1(CT11.2); NA88 (CT18); CTAGE (CT21); SPA17 (CT22); OY-TES-1 (CT23); CAGE(CT26); HOM-TES-85 (CT28); HCA661 (CT30); NY-SAR-35 (CT38); FATE (CT43);and TPTE (CT44).

Additional tumor antigens that can be targeted, including atumor-associated or tumor-specific antigen, include, but not limited to,alpha-actinin-4, Bcr-Abl fusion protein, Casp-8, beta-catenin, cdc27,cdk4, cdkn2a, coa-1, dek-can fusion protein, EF2, ETV6-AML1 fusionprotein, LDLR-fucosyltransferaseAS fusion protein, HLA-A2, HLA-A11,hsp70-2, KIAAO205, Mart2, Mum-1, 2, and 3, neo-PAP, myosin class I,OS-9, pml-RARα fusion protein, PTPRK, K-ras, N-ras, Triosephosphateisomeras, Bage-1, Gage 3,4,5,6,7, GnTV, Herv-K-mel, Lage-1,Mage-A1,2,3,4,6,10,12, Mage-C2, NA-88, NY-Eso-1/Lage-2, SP17, SSX-2, andTRP2-Int2, MelanA (MART-I), gp100 (Pmel 17), tyrosinase, TRP-1, TRP-2,MAGE-1, MAGE-3, BAGE, GAGE-1, GAGE-2, p15(58), CEA, RAGE, NY-ESO (LAGE),SCP-1, Hom/Mel-40, PRAME, p53, H-Ras, HER-2/neu, BCR-ABL, E2A-PRL,H4-RET, IGH-IGK, MYL-RAR, Epstein Barr virus antigens, EBNA, humanpapillomavirus (HPV) antigens E6 and E7, TSP-180, MAGE-4, MAGE-5,MAGE-6, p185erbB2, p180erbB-3, c-met, nm-23H1, PSA, TAG-72-4, CA 19-9,CA 72-4, CAM 17.1, NuMa, K-ras, β-Catenin, CDK4, Mum-1, p16, TAGE, PSMA,PSCA, CT7, telomerase, 43-9F, 5T4, 791Tgp72, α-fetoprotein, 13HCG,BCA225, BTAA, CA 125, CA 15-3 (CA 27.29\BCAA), CA 195, CA 242, CA-50,CAM43, CD68\KP1, CO-029, FGF-5, G250, Ga733 (EpCAM), HTgp-175, M344,MA-50, MG7-Ag, MOV18, NB\70K, NY—CO-1, RCAS1, SDCCAG16, TA-90 (Mac-2binding protein\cyclophilin C-associated protein), TAAL6, TAG72, TLP,and TPS. Other tumor-associated and tumor-specific antigens are known tothose of skill in the art and are suitable for targeting the disclosednanoparticles.

In some embodiments, the tumor antigen to be targeted isprostate-specific membrane antigen (PSMA). Thus, tumor targetingmoieties include any agonist, or antagonists of PSMA, or any derivativesthereof. In some embodiments, the tumor targeting moiety isS,S-2-[3-[5-amino-1-carboxypentyl]-ureido]-pentanedioic acid (ACUPA), orderivatives thereof.

ii. Antigens Associated with Tumor Neovasculature

The antigen may be specific to tumor neovasculature or may be expressedat a higher level in tumor neovasculature when compared to normalvasculature. Exemplary antigens that are over-expressed bytumor-associated neovasculature as compared to normal vasculatureinclude, but are not limited to, integrins including αvβ3, αvβ5, αvβ6,α2β1, α5β1, α6β1, and α6β4, VEGF/KDR, Tie2, vascular cell adhesionmolecule (VCAM), endoglin, and α₅β₃ integrin/vitronectin. Other antigensthat are over-expressed by tumor-associated neovasculature as comparedto normal vasculature are known to those of skill in the art and aresuitable for targeting by the nanoparticles.

In some embodiment, the antigen associated with tumor neovasculature tobe targated is integrin αvβ3. Thus, tumor targeting moieties include anyagonist, or antagonists of integrin αvβ3, or any derivatives thereof. Insome embodiments, the tumor targeting moiety is a disulfide-based cyclicarginine-glycine-aspartic acid (RGD) peptide called iRGD, that is,CRGDRGPDC (SEQ ID NO:11), or derivatives thereof. In some embodiments,iRGD is conjugated to one or more of the amphiphilic ploymers, forexample, in the form of iRGD-PEG-b-PDPA, as shown below in the Examples.In further embodiments, one or more of the amphiphilic ploymersconjugated with RGD include a membrane-penetrating motif such asoligoarginine. Examples include C₁₇H₃₅CONH-GR8GRGDS-OH (TCPA1);C₁₇H₃₅CONH—(C₁₇H₃₅CONH)KR8GRGDS-OH (TCPA2) shown in Exmaple 8.

iii. Chemokines/Chemokine Receptors

In another embodiment, the particles contain a domain that specificallybinds to a chemokine or a chemokine receptor. Chemokines are soluble,small molecular weight (8-14 kDa) proteins that bind to their cognateG-protein coupled receptors (GPCRs) to elicit a cellular response,usually directional migration or chemotaxis. Tumor cells secrete andrespond to chemokines, which facilitate growth that is achieved byincreased endothelial cell recruitment and angiogenesis, subversion ofimmunological surveillance and maneuvering of the tumoral leukocyteprofile to skew it such that the chemokine release enables the tumorgrowth and metastasis to distant sites. Thus, chemokines are vital fortumor progression.

Based on the positioning of the conserved two N-terminal cysteineresidues of the chemokines, they are classified into four groups namelyCXC, CC, CX3C and C chemokines. The CXC chemokines can be furtherclassified into ELR+ and ELR− chemokines based on the presence orabsence of the motif ‘glu-leu-arg (ELR motif)’ preceding the CXCsequence. The CXC chemokines bind to and activate their cognatechemokine receptors on neutrophils, lymphocytes, endothelial andepithelial cells. The CC chemokines act on several subsets of dendriticcells, lymphocytes, macrophages, eosinophils, natural killer cells butdo not stimulate neutrophils as they lack CC chemokine receptors exceptmurine neutrophils. There are approximately 50 chemokines and only 20chemokine receptors, thus there is considerable redundancy in thissystem of ligand/receptor interaction.

Chemokines elaborated from the tumor and the stromal cells bind to thechemokine receptors present on the tumor and the stromal cells. Theautocrine loop of the tumor cells and the paracrine stimulatory loopbetween the tumor and the stromal cells facilitate the progression ofthe tumor. Notably, CXCR2, CXCR4, CCR2 and CCR7 play major roles intumorigenesis and metastasis. CXCR2 plays a vital role in angiogenesisand CCR2 plays a role in the recruitment of macrophages into the tumormicroenvironment. CCR7 is involved in metastasis of the tumor cells intothe sentinel lymph nodes as the lymph nodes have the ligand for CCR7,CCL21. CXCR4 is mainly involved in the metastatic spread of a widevariety of tumors.

Any one or more of the above listed tumor antigens suitable fortargeting the nanoparticles to the site of tumor cells are alsoconsidered suitable to be used for therapeutic, and/or diagnosticpurposes such as knockdown targets by shRNA, and/or siRNA.

Other suitable oncogenic molecules as therapeutic, and/or diagnostictargets include molecules involved in tumor-associated pathways such asthose involved in cancer metabolism including glycolysis,glutaminolysis, autophagy (Galluzzi L et al., Nat Rev Drug Discov.12,829-846 (2013); Rubinsztein D C et al., Nat Rev Drug Discov. 2012September; 11(9): 709-730.). Other exemplary pathways associated withtumor cells include PI3/AKT pathway, Kelch-like ECH-associated protein 1(KEAP1)/NRF2 (nuclear factor, erythroid 2-like 2, NFE2L2) pathway,hypoxia-associated pathways, DNA repair pathways, and other pathwaysinvolved in cell division, apoptosis, cell cycle control.

Some exemplary metabolic targets for therapeutic, and/or diagnosticpurposes include glucose transporter (GLUTs), hexokinase,phosphofructokinase inhibitor, glyceraldehyde-3-phosphate dehydrogenase(GAPDH), phosphoglycerate mutase (PGM), enolase (ENO), lactatedehydrogenase, pyruvate dehydrogenase kinase (PDK), glucose-6-phosphatedehydrogenase (G6PD), tricarboxylic acid (TCA) cycle, monocarboxylatetransporter (MCTs), HSP90 inhibitor, CPT1, oxidative phosphorylation,glutamate dehydrogenase, mitochondrial citrate transporter SLC25A1(CIC), dihydroorotate dehydrogenase, neutral amino acid transporterSLC1A5, glutamate dehydrogenase 1 (GDH1); glutaminase (GLS); glutamateoxaloacetate transaminase 2(GOT2); γ-1-glutamyl-p-nitroanilide (GPNA);glutamate pyruvate transaminase 2(GPT2); L-type amino acid transporter 1(LAT1).

Additional targets for therapeutic, and/or diagnostic purposes are BET(bromodomain and extra-terminal) proteins including BRD2, BRD3, BRD4 andBRDT; kinesins including KIF11 (also known as EG5) andcentromere-associated protein E (CENPE); surviving (an inhibitor ofapoptosis protein), and prohibitin including PHB1 and PHB2.

b. Cancers to be Treated

The types of cancer that can be treated with the provided compositionsand methods include, but are not limited to, the following: bladder,brain, breast, cervical, colo-rectal, esophageal, kidney, liver, lung,nasopharangeal, pancreatic, prostate, skin, stomach, uterine, ovarian,testicular and the like. Administration is not limited to the treatmentof an existing tumors but can also be used to prevent or lower the riskof developing such diseases in an individual, i.e., for prophylacticuse. Potential candidates for prophylactic vaccination includeindividuals with a high risk of developing cancer, i.e., with a personalor familial history of certain types of cancer.

Malignant tumors which may be treated are classified herein according tothe embryonic origin of the tissue from which the tumor is derived.Carcinomas are tumors arising from endodermal or ectodermal tissues suchas skin or the epithelial lining of internal organs and glands.Sarcomas, which arise less frequently, are derived from mesodermalconnective tissues such as bone, fat, and cartilage. The leukemias andlymphomas are malignant tumors of hematopoietic cells of the bonemarrow. Leukemias proliferate as single cells, whereas lymphomas tend togrow as tumor masses. Malignant tumors may show up at numerous organs ortissues of the body to establish a cancer.

The cargo can be an anticancer agent for example anti-proliferativeagent, a pro-apoptotic agent, or other cytotoxic agent, including, butnot limited to, chemotherapeutic drugs and functional nucleic acids.

c. Preferred Cargos

The preferred cargos for treating cancers are known in the art andinclude, for example, anti-cancer agents and immunotherapeutic agents.

Representative anti-cancer agents include, but are not limited to,alkylating agents (such as cisplatin, carboplatin, oxaliplatin,mechlorethamine, cyclophosphamide, chlorambucil, dacarbazine, lomustine,carmustine, procarbazine, chlorambucil and ifosfamide), antimetabolites(such as fluorouracil (5-FU), gemcitabine, methotrexate, cytosinearabinoside, fludarabine, and floxuridine), antimitotics (includingtaxanes such as paclitaxel and decetaxel and vinca alkaloids such asvincristine, vinblastine, vinorelbine, and vindesine), anthracyclines(including doxorubicin, daunorubicin, valrubicin, idarubicin, andepirubicin, as well as actinomycins such as actinomycin D), cytotoxicantibiotics (including mitomycin, plicamycin, and bleomycin),topoisomerase inhibitors (including camptothecins such as camptothecin,irinotecan, and topotecan as well as derivatives of epipodophyllotoxinssuch as amsacrine, etoposide, etoposide phosphate, and teniposide),antibodies to vascular endothelial growth factor (VEGF) such asbevacizumab (AVASTIN®), other anti-VEGF compounds; thalidomide(THALOMID®) and derivatives thereof such as lenalidomide (REVLIMID®);endostatin; angiostatin; receptor tyrosine kinase (RTK) inhibitors suchas sunitinib (SUTENT®); tyrosine kinase inhibitors such as sorafenib(Nexavar®), erlotinib (Tarceva®), pazopanib, axitinib, and lapatinib;transforming growth factor-α or transforming growth factor-β inhibitors,and antibodies to the epidermal growth factor receptor such aspanitumumab (VECTIBIX®) and cetuximab (ERBITUX®).

In some embodiments, the particles include nucleic acid cargo,including, but not limited to functional nucleic acids, expressionconstructs or mRNA, or a combination thereof. For example, in someembodiments, a functional nucleic acid is designed to reduce expressionof an oncogene, for example a growth factor (e.g., c-Sis), mitogen,receptor tyrosine kinase (e.g., EGFR, PDGFR, VEGFR, HER2/neu),cytoplasmic tyrosine kinase (e.g., Src, Syk-ZAP-70, BTK families)cytoplasmic serine/threonine kinases (or a regulator subunit thereof)(e.g., Raf, cyclin-dependent kinases), regulatory GTPases (e.g., Ras),transcription factors (e.g., myc), angiogenesis (e.g., VEGF).

In some embodiments, the cargo is a functional nucleic acid that targetsa factor that contributes to chemotherapy resistance, for example, drugefflux pumps, anti-apoptotic defense mechanisms, etc. Specific targetsinclude, but are not limited to, glycoprotein (P-gp), Multidrugresistant protein 1(MRP-1), and B-cell lymphoma (BCL-2).RNAi-chemotherapeutic drug combinations have also been found to beeffective against different molecular targets as well and can increasethe sensitization of cancer cells to therapy several folds (Gandhi, etal., J Control Release. 2014 November 28; 0: 238-256).

Additionally or alternatively, mRNA can be introduced to enhance thefight against the tumor. For example, in some embodiments, the mRNA isdelivered into the cancer cells. Such mRNA can enhance apoptosis orsensitivity to drugs or other treatments such as radiation.

Functional nucleic acids, mRNA, or a combination thereof can beintroduced into cells that induce, program, or activate non-cancer cellsto attack the cancer cells. For example, in some embodiments, the cargois a nucleic acid that primes T cells or other immune cells forimmunotherapy against the cancer. Immunotherapeutic methods, includingCAR T cell therapy and other strategies for activation of immune cellsagainst target antigens, and inhibition of immune check points leadingto T cell exhaustion, anergy, or deactivation were well known in theart. The disclosed particles can be used in vitro or in vivo tointroduce nucleic acids into targets including immune cells, to, forexample, increase antigen-specific proliferation of T cells, enhancecytokine production by T cells, stimulate differentiation, stimulateeffector functions of T cells, promote T cell survival, overcome T cellexhaustion, overcome T cell anergy or a combination thereof. Immunecells, including but not limited to, neutrophils, lymphocytes, dendriticcells, macrophages, eosinophils, natural killer cells, can be the targetof therapy.

2. Inflammation and Infection

Methods of treating inflammation and infection are provided. Thenanoparticles can be designed, for example, for release in themicroenvironment of inflammation, injury, and infection, or immune orpro-inflammatory cells, or within immune or inflammatory cellsthemselves. Suitable methods can include administering a subject aneffective amount of nanoparticles containing a therapeutic cargo toreduce or alleviate one or more symptoms of the inflammation, injury, orinfection. The effect on the inflammation, injury, or infection can bedirect or indirect. Administration is not limited to the treatment of anexisting inflammation, injury, and infection, but can also be used toprevent or lower the risk of developing such diseases in an individual,i.e., for prophylactic use. A characteristic feature of the inflammationis local acidosis, which is attributed to the local increase oflactic-acid production by the anaerobic, glycolytic activity ofinfiltrated neutrophils and to the presence of short-chain, fatty acidby-products of bacterial metabolism (Grinstein, et al., Clin. Biochem.24,241-247 (1991) and Ehrich, W. E. (1961) Inflammation Allgower, M.eds. Progress in Surgery vol. 1,1-70 S. Karger Basel, Switzerland). Anacidic extracellular pH is also found in the epidermis and plays animportant protective role against bacterial infection (Lardner, et al.,Journal of Leukocyte Biology, 69(4):522-530 (2001)). As discussed above,local, tissue-specific increase in tissue temperature can occur at siteof inflammation, injury, and infection. Similar to selectively targetingthe tumor microenvironment, the pH and temperature sensitive particlescan be utilized to delivery and selectively release cargo at sites ofinflammation, injury, and infection.

As with cancer, in addition or alternative to selectively targetingcancer cells by targeting an acidic microenvironment, or one with anelevated temperature, cancer cells or their microenvironment can bespecifically targeted relative to healthy or normal cells by including atargeting moiety. Preferred targeting domains target the molecule toareas of inflammation, injury, or infection. Exemplary targeting domainsare antibodies, or antigen binding fragments thereof that are specificfor inflamed tissue or to a proinflammatory cytokine including but notlimited to IL17, IL-4, IL-6, IL-12, IL-21, IL-22, and IL-23. In the caseof neurological disorders such as Multiple Sclerosis, the targetingdomain may target the molecule to the CNS or may bind to VCAM-1 on thevascular epithelium. Additional targeting domains can be peptideaptamers specific for a proinflammatory molecule. In other embodiments,the particles can include a binding partner specific for a polypeptidedisplayed on the surface of an immune cell, for example a T cell. Instill other embodiments, the targeting domain specifically targetsactivated immune cells. Preferred immune cells that are targeted includeTh0, Th1, Th17 and Th22 T cells, other cells that secrete, or causeother cells to secrete inflammatory molecules including, but not limitedto, IL-1β, TNF-α, TGF-beta, IFN-γ, IL-17, IL-6, IL-23, IL-22, IL-21, andMMPs, and Tregs. For example, a targeting domain for Tregs may bindspecifically to CD25.

In some embodiments, the target site is neutrophils, which mayphagocytize the particles to release a therapeutic and/or diagnosticagent at the site of inflammation. Proteins constitutively expressed onthe surface of neutrophils that are important for recognition of theendothelial inflammatory signals include the glycoprotein P-selectinglycoprotein ligand-1 (PSGL-1) and L-selectin.

Other agents to be targeted include those associated with the disease.For example, a plaque targeted peptide can be one or more of thefollowing: Collagen IV, CREKA (SEQ ID NO:13), LyP-I, CRKRLDRNC (SEQ IDNO:14), or their combinations at various molar ratios.

In another embodiment, particles can contain a targeting domain totarget the molecule to an organ or tissue that is being transplanted.For example, the targeting domain can be an antibody, antigen bindingfragment thereof, or another binding partner specific for a polypeptidedisplayed on the surface of cells specific to the type of organ ortissue being transplanted.

a. Inflammation

Inflammation is typically a localized physical condition in which partof the body becomes reddened, swollen, hot, and often painful,especially as a reaction to injury or infection. Inflammation is aprotective response that involves immune cells, blood vessels, andmolecular mediators, the purpose of which is to eliminate the cause ofcell injury, remove necrotic cells and tissues damaged from the injuryand the inflammatory process, and to initiate tissue repair. Thecompositions can be used to treat acute and chronic inflammation.

The inflammation can be caused by an infection such as those describedbelow or can be caused by a non-infectious mechanism. For example,inflammation is associated with atherosclerosis, type IIIhypersensitivity, trauma, and ischaemia. Inflammation can be associatedwith autoimmune diseases, transplantation, graft verse host disease, andconditions driven by immune responses. In some embodiments, theparticles are used to deliver a cargo for treatment of an inflammatoryor autoimmune disease or disorder such as rheumatoid arthritis, systemiclupus erythematosus, alopecia areata, anklosing spondylitis,antiphospholipid syndrome, autoimmune Addison's disease, autoimmunehemolytic anemia, autoimmune hepatitis, autoimmune inner ear disease,autoimmune lymphoproliferative syndrome (alps), autoimmunethrombocytopenic purpura (ATP), Behcet's disease, bullous pemphigoid,cardiomyopathy, celiac sprue-dermatitis, chronic fatigue syndrome immunedeficiency, syndrome (CFIDS), chronic inflammatory demyelinatingpolyneuropathy, cicatricial pemphigoid, cold agglutinin disease, Crestsyndrome, Crohn's disease, Dego's disease, dermatomyositis,dermatomyositis—juvenile, discoid lupus, essential mixedcryoglobulinemia, fibromyalgia—fibromyositis, grave's disease,guillain-barre, hashimoto's thyroiditis, idiopathic pulmonary fibrosis,idiopathic thrombocytopenia purpura (ITP), Iga nephropathy, insulindependent diabetes (Type I), juvenile arthritis, Meniere's disease,mixed connective tissue disease, multiple sclerosis, myasthenia gravis,pemphigus vulgaris, pernicious anemia, polyarteritis nodosa,polychondritis, polyglancular syndromes, polymyalgia rheumatica,polymyositis and dermatomyositis, primary agammaglobulinemia, primarybiliary cirrhosis, psoriasis, Raynaud's phenomenon, Reiter's syndrome,rheumatic fever, sarcoidosis, scleroderma, Sjogren's syndrome, stiff-mansyndrome, Takayasu arteritis, temporal arteritis/giant cell arteritis,ulcerative colitis, uveitis, vasculitis, vitiligo, and Wegener'sgranulomatosis.

Preferred cargos for treating inflammation and autoimmune diseasesinclude, but are not limited to, anti-inflammatory agents andimmunosuppressive agents.

In some embodiments, the cargo is an immunosuppressive agents (e.g.,antibodies against other lymphocyte surface markers (e.g., CD40, alpha-4integrin) or against cytokines), other fusion proteins (e.g., CTLA-4-Ig(ORENCIA®), TNFR-Ig (Enbrel®)), TNF-α blockers such as Enbrel, Remicade,Cimzia and Humira, cyclophosphamide (CTX) (i.e. ENDOXAN®, CYTOXAN®,NEOSAR®, PROCYTOX®, REVIMMUNE™), methotrexate (MTX) (i.e. RHEUMATREX®,TREXALL®), belimumab (i.e. BENLYSTA®), or other immunosuppressive drugs(e.g., cyclosporin A, FK506-like compounds, rapamycin compounds, orsteroids), anti-proliferatives, cytotoxic agents, or other compoundsthat may assist in immunosuppression.

The cargo can function to inhibit or reduce T cell activation andcytokine production. In one such embodiment, the additional therapeuticagent is a CTLA-4 fusion protein, such as CTLA-4 Ig (ABATACEPT®). CTLA-4Ig fusion proteins compete with the co-stimulatory receptor, CD28, on Tcells for binding to CD80/CD86 (B7-1/B7-2) on antigen presenting cells,and thus function to inhibit T cell activation. In a preferredembodiment, the additional therapeutic agent is a CTLA-4-Ig fusionprotein known as BELATACEPT®. BELATACEPT® contains two amino acidsubstuitutions (L104E and A29Y) that markedly increase its avidity toCD86 in vivo. In another embodiment, the additional therapeutic agent isMaxy-4.

The cargo can treat chronic transplant rejection or GvHD, whereby thetreatment regimen effectively targets both acute and chronic transplantrejection or GvHD. In a preferred embodiment the second therapeutic is aTNF-α blocker.

The cargo can increase the amount of adenosine in the serum, see, forexample, WO 08/147482. In a preferred embodiment, the second therapeuticis CD73-Ig, recombinant CD73, or another agent (e.g. a cytokine ormonoclonal antibody or small molecule) that increases the expression ofCD73, see for example WO 04/084933. In another embodiment the secondtherapeutic agent is Interferon-beta.

The cargo can increase Treg activity or production. Exemplary Tregenhancing agents include but are not limited to glucocorticoidfluticasone, salmeteroal, antibodies to IL-12, IFN-γ, and IL-4; vitaminD3, and dexamethasone, and combinations thereof. Antibodies to otherproinflammatory molecules can also be used. Preferred antibodies bind toIL-6, IL-23, IL-22 or IL-21.

The cargo can be a rapamycin compound. As used herein the term“rapamycin compound” includes the neutral tricyclic compound rapamycin,rapamycin derivatives, rapamycin analogs, and other macrolide compoundswhich are thought to have the same mechanism of action as rapamycin(e.g., inhibition of cytokine function). The language “rapamycincompounds” includes compounds with structural similarity to rapamycin,e.g., compounds with a similar macrocyclic structure, which have beenmodified to enhance their therapeutic effectiveness. Exemplary Rapamycincompounds are known in the art (See, e.g. WO95122972, WO 95116691, WO95104738, U.S. Pat. Nos. 6,015,809; 5,989,591; 5,567,709; 5,559,112;5,530,006; 5,484,790; 5,385,908; 5,202,332; 5,162,333; 5,780,462;5,120,727).

The language “FK506-like compounds” includes FK506, and FK506derivatives and analogs, e.g., compounds with structural similarity toFK506, e.g., compounds with a similar macrocyclic structure which havebeen modified to enhance their therapeutic effectiveness. Examples ofFK506-like compounds include, for example, those described in WO00101385. In some embodiments, the language “rapamycin compound” doesnot include “FK506-like compounds.”

Other suitable therapeutics include, but are not limited to,anti-inflammatory agents. The anti-inflammatory agent can benon-steroidal, steroidal, or a combination thereof. Representativeexamples of non-steroidal anti-inflammatory agents include, withoutlimitation, oxicams, such as piroxicam, isoxicam, tenoxicam, sudoxicam;salicylates, such as aspirin, disalcid, benorylate, trilisate, safapryn,solprin, diflunisal, and fendosal; acetic acid derivatives, such asdiclofenac, fenclofenac, indomethacin, sulindac, tolmetin, isoxepac,furofenac, tiopinac, zidometacin, acematacin, fentiazac, zomepirac,clindanac, oxepinac, felbinac, and ketorolac; fenamates, such asmefenamic, meclofenamic, flufenamic, niflumic, and tolfenamic acids;propionic acid derivatives, such as ibuprofen, naproxen, benoxaprofen,flurbiprofen, ketoprofen, fenoprofen, fenbufen, indopropfen, pirprofen,carprofen, oxaprozin, pranoprofen, miroprofen, tioxaprofen, suprofen,alminoprofen, and tiaprofenic; pyrazoles, such as phenylbutazone,oxyphenbutazone, feprazone, azapropazone, and trimethazone. Mixtures ofthese non-steroidal anti-inflammatory agents may also be employed.

Representative examples of steroidal anti-inflammatory drugs include,without limitation, corticosteroids such as hydrocortisone,hydroxyl-triamcinolone, alpha-methyl dexamethasone,dexamethasone-phosphate, beclomethasone dipropionates, clobetasolvalerate, desonide, desoxymethasone, desoxycorticosterone acetate,dexamethasone, dichlorisone, diflorasone diacetate, diflucortolonevalerate, fluadrenolone, fluclorolone acetonide, fludrocortisone,flumethasone pivalate, fluosinolone acetonide, fluocinonide, flucortinebutylesters, fluocortolone, fluprednidene (fluprednylidene) acetate,flurandrenolone, halcinonide, hydrocortisone acetate, hydrocortisonebutyrate, methylprednisolone, triamcinolone acetonide, cortisone,cortodoxone, flucetonide, fludrocortisone, difluorosone diacetate,fluradrenolone, fludrocortisone, diflurosone diacetate, fluradrenoloneacetonide, medrysone, amcinafel, amcinafide, betamethasone and thebalance of its esters, chloroprednisone, chlorprednisone acetate,clocortelone, clescinolone, dichlorisone, diflurprednate, flucloronide,flunisolide, fluoromethalone, fluperolone, fluprednisolone,hydrocortisone valerate, hydrocortisone cyclopentylpropionate,hydrocortamate, meprednisone, paramethasone, prednisolone, prednisone,beclomethasone dipropionate, triamcinolone, and mixtures thereof.

In some embodiments, the cargo is a functional nucleic acid that targetsa factor that contributes to inflammation, the activation or persistenceof pro-inflammatory cells, a pro-inflammatory response, active immuneresponse, an autoimmune response, etc. Specific targets include, forexample, pro-inflammatory molecules such as IL-1β, TNF-α, TGF-beta,IFN-γ, IL-17, IL-6, IL-23, IL-22, IL-21, and MMPs.

Additionally or alternatively, mRNA can be introduced to reduce theinflammation or autoimmune response.

Functional nucleic acids, mRNA, or a combination thereof can beintroduced into cells that inhibit the development of naïve T cells intoTh1, Th17, Th22 or other cells that secrete, or cause other cells tosecrete, inflammatory molecules. The cargo can increase the number oractivity of Tregs. The cargo can promote or enhance production of IL-10or another anti-inflammatory cytokine. In some embodiments, the cargoenhances the differentiation, recruitment and/or expansion of Treg cellsin the region of inflammation, autoimmune activity, or tissueengraftment. Exemplary functional nucleic acid targets for treatingautoimmune disease are reviewed in Pauley and Cha, Pharmaceuticals 2013,6(3), 287-294; and discussed in, for example, Kim, et al., MolecularTherapy, (2010) 18 5, 993-1001, Laroui, et al., Molecular Therapy(2014); 221, 69-80, Ponnappa, et al., Curr Opin Investig Drugs. 2009May; 10(5):418-24; Abrams, et al., Molecular Therapy, (2010) 18 1,171-180, Leuschner, et al., Nature biotechnology 29.11 (2011):1005-1010. PMC. Web. 29 Mar. 2016.

In some embodiments, the cargo is a nucleic acid that encodes ananti-inflammatory cytokine, for example, (IL)-1 receptor antagonist,IL-4, IL-6, IL-10, IL-11, or IL-13 (Opal and DePalo, et al., Chest.(2000) 117(4):1162-72).

b. Infections

Similarly, in some embodiments, the disclosed particles are used todeliver a cargo for treatment of an infectious disease. Infectiousdiseases that can be treated, prevented, and/or managed using thedisclosed nanoparticles can be caused by infectious agents including butnot limited to bacteria, fungi, protozae, and viruses. Viral diseasesinclude, for example, those caused by hepatitis type A, hepatitis typeB, hepatitis type C, influenza (e.g., influenza A or influenza B),varicella, adenovirus, herpes simplex type I (HSV-I), herpes simplextype II (HSV-II), rinderpest, rhinovirus, echovirus, rotavirus,respiratory syncytial virus, papilloma virus, papova virus,cytomegalovirus, echinovirus, arbovirus, huntavirus, coxsackie virus,mumps virus, measles virus, rubella virus, polio virus, small pox,Epstein Barr virus, human immunodeficiency virus type I (HIV-I), humanimmunodeficiency virus type II (HIV-II), and agents of viral diseasessuch as viral meningitis, encephalitis, dengue or small pox.

Bacterial diseases can be caused by bacteria (e.g., Escherichia coli,Klebsiella pneumoniae, Staphylococcus aureus, Enterococcus faecalis,Proteus vulgaris, Staphylococcus viridans, and Pseudomonas aeruginosa)include, for example, mycobacteria rickettsia, mycoplasma, neisseria, S.pneumonia, Borrelia burgdorferi (Lyme disease), Bacillus antracis(anthrax), tetanus, streptococcus, staphylococcus, mycobacterium,pertissus, cholera, plague, diptheria, chlamydia, S. aureus andlegionella.

Protozoal diseases caused by protozoa include, for example, leishmania,kokzidioa, trypanosome schistosoma or malaria. Parasitic diseases causedby parasites include chlamydia and rickettsia.

Fungal infections include, but are not limited to, Candida infections,zygomycosis, Candida mastitis, progressive disseminated trichosporonosiswith latent trichosporonemia, disseminated candidiasis, pulmonaryparacoccidioidomycosis, pulmonary aspergillosis, Pneumocystis cariniipneumonia, cryptococcal meningitis, coccidioidal meningoencephalitis andcerebrospinal vasculitis, Aspergillus niger infection, Fusariumkeratitis, paranasal sinus mycoses, Aspergillus fumigatus endocarditis,tibial dyschondroplasia, Candida glabrata vaginitis, oropharyngealcandidiasis, X-linked chronic granulomatous disease, tinea pedis,cutaneous candidiasis, mycotic placentitis, disseminatedtrichosporonosis, allergic bronchopulmonary aspergillosis, mycotickeratitis, Cryptococcus neoformans infection, fungal peritonitis,Curvularia geniculata infection, staphylococcal endophthalmitis,sporotrichosis, and dermatophytosis.

Prepared cargo for treating infections can including anti-infectivessuch as Difloxacin Hydrochloride; Lauryl Isoquinolinium Bromide;Moxalactam Disodium; Ornidazole; Pentisomicin; SarafloxacinHydrochloride; Protease inhibitors of HIV and other retroviruses;Integrase Inhibitors of HIV and other retroviruses; Cefaclor (Ceclor);Acyclovir (Zovirax); Norfloxacin (Noroxin); Cefoxitin (Mefoxin);Cefuroxime axetil (Ceftin); or Ciprofloxacin (Cipro).

In some embodiments, the cargo is antibiotic such as a beta-lactam(e.g., penicillins, cephalosporins, monobactams, and carbapenems), acephalosporins, a monobactam, a carbapenem, a macrolide, a lincosamide,streptogramin, an aminoglycoside, a quinolone, a sulfonamide, atetracycline, a glyopeptide, lipoglycopeptide, rifamycin, a polypeptide,or a tuberactinomycin.

In some embodiments, the cargo is a functional nucleic acid that targetsa factor that contributes to anti-infective drug resistance, forexample, drug efflux pumps, anti-apoptotic defense mechanisms, etc., orinfected cells or the pathogens themselves. In some embodiments, thefunctional nucleic acid specifically targets a gene expressed by thepathogen. See, for example, Fischer, et al., Cell Research, (2004) 14,460-466, which describes RNAi strategies for targeting viral infection.Additionally or alternatively, mRNA can be introduced to enhance thefight against the infection.

As in described above in the context of cancer, functional nucleicacids, mRNA, or a combination thereof can be introduced into cells thatinduce, program, or activate cells to resolve an infection. For example,in some embodiments, the cargo is a nucleic acid that primes T cells orother immune cells for immunotherapy against the infection.Immunotherapeutic methods, including CAR T cell therapy and otherstrategies for activation of immune cells against target antigens, andinhibition of immune check points leading to T cell exhaustion, anergy,or deactivation were well known in the art. The disclosed particles canbe used in vitro or in vivo to introduce nucleic acids into targetsincluding immune cells, to, for example, increase antigen-specificproliferation of T cells, enhance cytokine production by T cells,stimulate differentiation, stimulate effector functions of T cells,promote T cell survival, overcome T cell exhaustion, overcome T cellanergy or a combination thereof. Immune cells, including but not limitedto, neutrophils, lymphocytes, dendritic cells, macrophages, eosinophils,natural killer cells, can be the target of therapy.

The present invention will be further understood by reference to thefollowing non-limiting examples.

Example 1: Ultra pH-Responsive and Tumor-Penetrating Nanoplatform forTargeted siRNA Delivery with Robust Anti-Cancer Efficacy Methods andMaterials Materials

Methoxyl-polyethylene glycol (Meo-PEG₁₁₃-OH) and hydroxyl polyethyleneglycol carboxylic acid (HO-PEG₁₁₃-COOH) were purchased from JenKemTechnology and used as received. Internalizing RGD (iRGD) with thesequence CRGDRGPDC (SEQ ID NO:11) was obtained from GL Biochem Ltd.2-(Diisopropyl amino) ethyl methacrylate (DPA-MA), glycidyl methacrylate(GMA), and methyl methacrylate (MMA) were provided by Sigma-Aldrich andpassed over an alumina column before use in order to remove thehydroquinone inhibitors. α-Bromoisobutyryl bromide, triethylamine (TEA),N,N,N′,N′,N′-pentamethyldiethylenetriamine (PMDETA), copper (I) bromide(CuBr), N,N′-dimethylformamide (DMF), tetraethylenepentamine (TEPA),1,2-epoxyhexadecane, isopropyl alcohol, and dichloromethane (DCM) wereacquired from Sigma-Aldrich and used directly. Lipofectamine 2000(Lipo2K) was purchased from Invitrogen. Steady-Glo luciferase assaysystem was provided by Promega. GL3, fluorescent dye (DY547, DY647 andDY677) labeled GL3 and survivin siRNAs were acquired from Dharmacon. ThesiRNA sequences are as follows: GL3 siRNA, 5′-CUU ACG CUG AGU ACU UCGAdTdT-3′ (sense) (SEQ ID NO:1) and 5′-UCG AAG UAC UCA GCG UAA GdTdT-3′(antisense)) (SEQ ID NO:2); survivin siRNA, 5′-GGA CCA CCG CAU CUC UACAdTdT-3′ (sense) (SEQ ID NO:3) and 5′-UGU AGA GAU GCG GUG GCU CdTdT-3′(antisense) (SEQ ID NO:4). PHB1 siRNA, 5′-GCG ACG ACC UUA CAG AGC GUU-3′(sense) (SEQ ID NO:5) and 5′-CGC UCU GUA AGG UCG UCG CUU-3′ (antisense)(SEQ ID NO:6); KIF11 siRNA, 5′-GAA UAG GGU UAC AGA GUU GUU-3′ (sense)(SEQ ID NO:7) and 5′-CAA CUC UGU AAC CCU AUU CUU-3′ (antisense) (SEQ IDNO:8). The fluorescent dyes DY547 and DY647 were labeled at the 5′-endof the sense strand of GL3 siRNA. DY677 was labeled at the 5′-end ofboth the sense and antisense strands of GL3 siRNA. HeLa cells stablyexpressing firefly and Renilla luciferase (Luc-HeLa) were obtained fromAlnylam Pharmaceuticals, Inc. The cells were incubated in RPMI-1640medium (Invitrogen) with 10% fetal bovine serum (FBS, Sigma-Aldrich) and1% penicillin/streptomycin (Sigma-Aldrich). All other reagents andsolvents are of analytical grade and used without further purification.

Synthesis of Meo-PEG-Br and Br-PEG-COOH

Meo-PEG₁₁₃-OH (8 g, 1.6 mmol) and TEA (1.3 mL, 9.6 mmol) were dissolvedin 250 mL of DCM. In an ice-salt bath, α-bromoisobutyryl bromide (1 mL,8 mmol) dissolved in 10 mL of DCM was added dropwise. After stirring for24 h, the mixture was washed with 1 M NaOH (3×50 mL), 1 M HCl (3×50 mL),and deionized water (3×50 mL), respectively. After drying over anhydrousMgSO₄, the solution was concentrated, and cold ether was added toprecipitate the product. After re-precipitation thrice, the product wascollected as white powder after drying under vacuum. The synthesis ofBr-PEG-COOH was carried out according to a method similar to thatdescribed above, by changing Meo-PEG₁₁₃₋OH with HO-PEG₁₁₃-COOH. Thesynthesis scheme of Br-PEG-COOH is shown below.

Synthesis of methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate) (Meo-PEG-b-P(DPA-co-GMA))

Meo-PEG-b-P(DPA-co-GMA) copolymers with different compositions weresynthesized by atom transfer radical polymerization (ATRP).Meo-PEG₁₁₃-b-P(DPA₈₀-co-GMA₅) is used as an example to illustrate theprocedure. DPA-MA (2.6 g, 12 mmol), GMA (0.11 g, 0.75 mmol), Meo-PEG-Br(0.75 g, 0.15 mmol), and PMDETA (31.5 μL, 0.15 mmol) were added to apolymerization tube. DMF (3 mL) and 2-propanol (3 mL) were then added todissolve the monomer and initiator. After three cycles offreeze-pump-thaw to remove oxygen, CuBr (21.6 mg, 0.15 mmol) was addedunder nitrogen atmosphere and the polymerization tube was sealed undervacuum. After polymerization at 40° C. for 24 h, tetrahydrofuran (THF)was added to dilute the product, which was then passed through a neutralAl₂O₃ column to remove the catalyst. The resulting THF solution wasconcentrated and the residue was dialyzed against THF, followed bydeionized water. The expected copolymer was collected as a white powderafter freeze-drying under vacuum. The synthesis scheme is shown below.The feed compositions of the copolymers are summarized in Table 1.

TABLE 1 Feed compositions and characterizations ofMeo-PEG-b-P(DPA-co-GMA) Repeat unit Repeat unit M_(n, GPC) M_(n, NMR)No. (DPA) a (GMA) a (×10⁻⁴ Da) b PDI b (×10⁻⁴ Da) a pKa c PDPA40-GMA5 395 1.44 1.19 1.42 6.34 PDPA50-GMA5 50 5 1.68 1.12 1.66 6.31 PDPA60-GMA558 5 1.69 1.18 1.83 6.29 PDPA70-GMA5 69 5 1.94 1.24 2.06 6.26PDPA80-GMA5 80 5 2.19 1.29 2.29 6.24 PDPA100-GMA5 99 5 2.87 1.14 2.716.21 a Determined by ¹HNMR using CDCl₃ as solvent. b Number-averaged(Mn) and polydispersity index (PDI) were determined by GPC using THF asthe eluent.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA)

Meo-PEG-b-P(DPA-co-GMA-TEPA) was synthesized via the ring openingreaction between TEPA and the epoxy group of GMA repeating unit. Inbrief, Meo-PEG-b-P(DPA-co-GMA) (1.5 g) dissolved in DMF (20 mL) wasadded dropwise to the DMF solution (5 mL) of TEPA (30-fold molar excessrelative to the GMA repeating unit). After reaction at 60° C. for 7 h,the mixture was transferred to a dialysis tube and then dialyzed againstdeionized water. The Meo-PEG-b-P(DPA-co-GMA-TEPA) was finally collectedas a white powder after freeze-drying under vacuum. The synthesis routeof Meo-PEG-b-P(DPA-co-GMA-TEPA) is shown below.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)

Meo-PEG-b-P(DPA-co-GMA-TEPA) (1 g) and 1,2-epoxyhexadecane (equal molaramount relative to TEPA repeating unit) were dissolved in DMF (20 mL)and the solution was stirred at 70° C. for 5 h. Subsequently, thesolution was transferred to a dialysis tube and then dialyzed againstDMF, followed by deionized water. The Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)was obtained as a white powder after freeze-drying under vacuum. Thedetailed synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) is shown below.Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5)

Meo-PEG-b-P(DPA-co-GMA-TEPA) (0.2 g) and Cy5.5 NHS ester (1.5-fold molarexcess relative to the TEPA repeating unit) were well dissolved in 5 mLof THF. After constantly stirring in dark for 48 h, the solution wasdialyzed against deionized water and the product was collected afterfreeze-drying. The synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5) isshown below.

Synthesis Scheme of Meo-PEG-b-P(DPA-Co-GMA-TEPA-Cy5.5)

Synthesis of HOOC-PEG-b-PDPA

HOOC-PEG-b-PDPA copolymers were also synthesized by the ATRP method.DPA-MA (1.73 g, 8 mmol), Br-PEG-COOH (0.5 g, 0.1 mmol), and PMDETA (21μL, 0.1 mmol) were added to a polymerization tube. Subsequently, DMF (2mL) and 2-propanol (2 mL) were added to dissolve the monomer andinitiator. After three cycles of freeze-pump-thaw to remove oxygen, CuBr(14.4 mg, 0.1 mmol) was added under nitrogen atmosphere and thepolymerization tube was sealed under vacuum. After polymerization at 40°C. for 24 h, tetrahydrofuran (THF) was added to dilute the product,which was then passed through a neutral Al₂O₃ column to remove thecatalyst. The obtained THF solution was concentrated and the residue wasdialyzed against deionized water. The HOOC-PEG-b-PDPA was obtained as awhite powder after freeze-drying under vacuum. The synthesis scheme isshown below. The feed compositions are summarized in Table 2.

TABLE 2 Feed compositions and characterizations of HOOC-PEG-b- PDPARepeat unit M_(n,GPC) M_(n,NMR) No. (DPA) a (×10⁻⁴ ) b PDI b (×10⁻⁴ Da)a HOOC-PEG-_(b)-PDPA₄₀ 36 1.31 1.34 1.27 HOOC-PEG-_(b)-PDPA₅₀ 45 1.491.28 1.48 HOOC-PEG-_(b)-PDPA₆₀ 55 1.76 1.29 1.69 HOOC-PEG-_(b)-PDPA₇₀ 641.92 1.27 1.89 HOOC-PEG-_(b)-PDPA₈₀ 76 2.04 1.24 2.14HOOC-PEG-_(b)-PDPA₁₀₀ 92 2.57 1.19 2.48 a Determined by ¹HNMR usingCDCl₃ as solvent. b Number-averaged (Mn) and polydispersity index (PDI)were determined by GPC using THF as the eluent.

Synthesis of iRGD-PEG-b-PDPA

HOOC-PEG-b-PDPA copolymer (0.2 g), iRGD peptide (1.5-fold molar excessrelative to the terminal carboxylic acid group), EDC.HCl (3-fold molarexcess relative to the terminal carboxylic acid group), and NHS (3-foldmolar excess relative to the terminal carboxylic acid group) were welldissolved in pH 5.0 water. The mixture was stirred at room temperaturefor 48 h. The solution was subsequently dialyzed against deionized waterand the expected iRGD-PEG-PDPA was collected after freeze-drying.

Synthesis Scheme of iRGD-PEG-b-PDPA

Synthesis of Control Copolymers

The control copolymers, methoxyl-polyethylene glycol-b-poly (methylmethacrylate-co-glycidyl methacrylate) (Meo-PEG₁₁₃-b-P(MMA₈₀-co-GMA₅))Meo-PEG₁₁₃-b-P(MMA₈₀-co-GMA₅-TEPA₅), HOOC-PEG₁₁₃-b-PMMA₈₀,iRGD-PEG₁₁₃-b-PMMA₈₀, and Meo-PEG₁₁₃-b-P(MMA₈₀-co-GMA₅-TEPA₅-C14) weresynthesized according to the method described above, by changing themonomer DPA-MA with MMA. The chemical structure of iRGD-PEG₁₁₃-b-PMMA₈₀and Meo-PEG₁₁₃-b-P(MMA₈₀-co-GMA₅-TEPA₅-C14) is shown below.

Gel Permeation Chromatography (GPC)

Number- and weight-average molecular weights (M_(n) and M_(w),respectively) of the polymers were determined by a gel permeationchromatographic system equipped with a Waters 2690D separations moduleand a Waters 2410 refractive index detector. THF was used as the eluentat a flow rate of 0.3 mL/min. Waters millennium module software was usedto calculate molecular weight on the basis of a universal calibrationcurve generated by polystyrene standard of narrow molecular weightdistribution.

¹H Nuclear magnetic resonance (¹HNMR)

The ¹HNMR spectra of the polymers were recorded on a Mercury VX-300spectrometer at 400 MHz (Varian, USA), using CDCl₃ as a solvent and TMSas an internal standard.

Acid-Base Titration

Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) was dispersed in deionized water, and aconcentrated HCl aqueous solution was added until complete dissolutionof the copolymer (1 mg/mL). Subsequently, 1 M NaOH aqueous solution wasadded in 1-5 μL increments. After each addition, the solution wasconstantly stirred for 3 min, and the solution pH was measured using apH meter. The pK_(a) of the copolymer was determined as the pH at which50% copolymer turns ionized.

Preparation and Characterization of Nanoparticles (NPs)

Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) was dissolved in THF to form ahomogenous solution with a concentration of 4 mg/mL. Subsequently, acertain volume of this THF solution was taken and mixed with 1 nmolsiRNA (0.1 nmol/4 aqueous solution) in a N/P molar ratio of 40:1. Undervigorous stirring (1000 rpm), the mixture was added dropwise to 2.5 mLof deionized water. The NP dispersion formed was transferred to anultrafiltration device (EMD Millipore, MWCO 100 K) and centrifuged toremove the organic solvent and free compounds. After washing with PBS(pH 7.4) solution (3×5 mL), the siRNA loaded NPs were dispersed in 1 mLof phosphate buffered saline (PBS, pH 7.4) solution. Size and zetapotential were determined by dynamic light scattering (DLS, BrookhavenInstruments Corporation). The morphology of NPs was visualized on aTecnai G2 Spirit BioTWIN transmission electron microscope (TEM). Beforeobservation, the sample was stained with 1% uranyl acetate and driedunder air. To determine siRNA encapsulation efficiency, DY547-labelledGL3 siRNA loaded NPs were prepared according to the method describedabove. A small volume (50 μL) of the NP solution was withdrawn and mixedwith 20-fold DMSO. The fluorescence intensity of DY547-labelled GL3siRNA was measured using a Synergy HT multi-mode microplate reader(BioTek Instruments) and compared to the free DY547-labelled GL3 siRNAsolution (1 nmol/mL PBS solution).

To prepare the iRGD-NPs, Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) (4 mg/mL inTHF) was mixed with 1 nmol siRNA (0.1 nmol/4 aqueous solution) in a N/Pmolar ratio of 40:1. Then iRGD-PEG-b-PDPA (4 mg/mL in THF, 10 mol %compared to Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)) was added, and the mixturewas added dropwise to 2.5 mL of deionized water. The iRGD-NPs werepurified by an ultrafiltration device (EMD Millipore, MWCO 100 K) andfinally dispersed in 1 mL of PBS. The siRNA encapsulation efficiency wasexamined by replacing the siRNA with DY547-labelled GL3 siRNA.

Evaluation of pH Responsiveness

The THF solution of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) (4 mg/mL) andMeo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5) (4 mg/mL) was mixed in a volume ratioof 8:2. Under vigorously stirring (1000 rpm), 0.5 mL of the mixture wasadded dropwise to 5 mL of deionized water. After collection andpurification by an ultrafiltration device (EMD Millipore, MWCO 100 kDa),the NPs formed were dispersed in 1 mL of deionized water. Subsequently,1 M NaOH or HCl was added in 1-5 μL increments, and the fluorescenceintensity of the NPs was measured on a Synergy HT multi-mode microplatereader. The normalized fluorescence intensity (NFI) vs. pH profile wasused to quantitatively assess the pH responsiveness. NFI is calculatedas follows:

NFI=(F−/(F _(max) −F _(mm))

where F is the fluorescence intensity of the NPs at any given pH valueand F_(max) and F_(min) are the maximal and minimal fluorescenceintensity of the NPs, respectively.

In Vitro siRNA Release

DY547-labelled GL3 siRNA-loaded NPs were prepared as described above.Subsequently, the NPs were dispersed in 1 mL of PBS (pH 7.4) and thentransferred to a Float-a-lyzer G2 dialysis device (MWCO 100 kDa,Spectrum) that was immersed in PBS (pH 7.4) at 37° C. At a predeterminedinterval, 5 μL, of the NP solution was withdrawn and mixed with 20-foldDMSO. The fluorescence intensity of DY547-labelled siRNA was determinedby Synergy HT multi-mode microplate reader.

Cell Culture

Human cervical cancer cell line with the expression of luciferase(Luc-HeLa) and prostate cancer cell line (PC3) were incubated inRPMI1640 medium with 10% FBS at 37° C. in a humidified atmospherecontaining 5% CO₂.

Luciferase Silencing.

Luc-HeLa cells were seeded in 96-well plates (5,000 cells per well) andincubated in 0.1 mL of RPMI1640 medium with 10% FBS for 24 h.Thereafter, the GL3 siRNA-loaded NPs were added. After 24 h incubation,the cells were washed with fresh medium and allowed to incubate foranother 48 h. The expression of firefly luciferase in HeLa cells wasdetermined using Steady-Glo luciferase assay kits. Cytotoxicity wasmeasured using alamarBlue assay according to the manufacturer'sprotocol. The luminescence or fluorescence intensity was measured usinga microplate reader, and the average value of three independentexperiments was collected. As a control, the silencing effect ofLipo2K/GL3 siRNA complexes was also evaluated according to the proceduredescribed above and compared to that of GL3 siRNA-loaded NPs.

Determination of the Expression of Integrins α_(v)β₃ and α_(v)β₅

Luc-HeLa and PC3 cells were seeded in 6-well plates (50,000 cells perwell) and incubated in 1 mL of RPMI1640 medium containing 10% FBS for 24h. Thereafter, 10 μL of FITC-conjugated anti-human CD51/61 antibody(BioLegend) or FITC-conjugated anti-human integrin α_(v)β₅ antibody (EMDMillipore) were added, and the cells were allowed to incubate foranother 4 h. After removing the medium and washing with PBS (pH 7.4)solution thrice, the cells were collected for flow cytometryquantitative analysis (BD FACSAria™ III, USA).

Confocal Laser Scanning Microscope (CLSM)

Luc-HeLa and PC3 cells (20,000 cells) were seeded in discs and incubatedin 1 mL of RPMI1640 medium containing 10% FBS for 24 h. Subsequently,the DY547-labelled GL3 siRNA-loaded NPs or iRGD-NPs were added, and thecells were allowed to incubate for 1 or 4 h. After removing the mediumand subsequently washing with PBS (pH 7.4) solution thrice, theendosomes and nuclei were stained by lysotracker green and Hoechst33342, respectively. The cells were then viewed under a FV1000 CLSM(Olympus).

Flow Cytometry

Luc-HeLa and PC3 cells were seeded in 6-well plates (50,000 cells perwell) and incubated in 1 mL of RPMI1640 medium containing 10% FBS for 24h. Subsequently, the DY547-labelled GL3 siRNA-loaded NPs or iRGD-NPswere added, and the cells were allowed to incubate for another 4 h.After removing the medium and subsequently washing with PBS (pH 7.4)solution thrice, the cells were collected for flow cytometryquantitative analysis.

In Vitro Survivin Silencing

PC3 cells were seeded in 6-well plates (50,000 cells per well) andincubated in 1 mL of RPMI1640 medium containing 10% FBS for 24 h.Subsequently, the cells were transfected with the survivin siRNA-loadedNPs or iRGD-NPs for 24 h. After washing the cells with PBS thrice, thecells were further incubated in fresh medium for another 48 h.Thereafter, the cells were digested by trypsin and the proteins wereextracted using modified radioimmunoprecipitation assay lysis buffer (50mM Tris-HCl pH 7.4, 150 mM NaCl, 1% NP-40 substitute, 0.25% sodiumdeoxycholate, 1 mM sodium fluoride, 1 mM Na₃VO₄, 1 mM EDTA),supplemented with protease inhibitor cocktail and 1 mMphenylmethanesulfonyl fluoride (PMSF). The expression of survivin wasexamined using the western blot analysis described below.

Western Blot Analysis

Equal amounts of protein, as determined with a bicinchoninic acid (BCA)protein assay kit (Pierce/Thermo Scientific) according to themanufacturer's instructions, were added to SDS-PAGE gels and separatedby gel electrophoresis. After transferring the proteins from gel topolyvinylidene difluoride membrane, the blots were blocked with 3% BSAin TBST (50 mM Tris-HCl pH 7.4, 150 mM NaCl, and 0.1% Tween 20) and thenincubated with a mixture of survivin rabbit antibody (Cell Signaling)and beta-actin rabbit antibody (Cell Signaling). The expression ofsurvivin was detected with horseradish peroxidase (HRP)-conjugatedsecondary antibody (anti-rabbit IgG HRP-linked antibody, Cell Signaling)and an enhanced chemiluminescence (ECL) detection system (Pierce).

In Vitro Cell Proliferation

PC3 cells were seeded in 6-well plates (20,000 cells per well) andincubated in 1 mL of RPMI1640 medium containing 10% FBS for 24 h.Thereafter, the cells were transfected with the survivin siRNA-loadedNPs or iRGD-NPs for 24 h and then washed with fresh medium for furtherincubation. At predetermined intervals, the cytotoxicity was measured byalamarBlue assay according to the manufacturer's protocol. After eachmeasurement, the alamarBlue agent was removed and the cells wereincubated in fresh medium for further proliferation.

Animals

Healthy male BALB/c mice (4-5 weeks old) were purchased from CharlesRiver Laboratories. All in vivo studies were performed in accordancewith National Institutes of Health animal care guidelines and in strictpathogen-free conditions in the animal facility of Brigham and Women'sHospital. Animal protocol was approved by the Institutional Animal Careand Use Committees on animal care (Harvard Medical School).

PC3 Xenograft Tumor Model

The tumor model was constructed by subcutaneous injection with 200 μL ofPC3 cell suspension (a mixture of RPMI 1640 medium and Matrigel in 1:1volume ratio) with a density 1×10⁷ cells/mL into the back region ofhealthy male BALB/c nude mice. When the volume of the PC3 tumorxenograft reached ˜100 mm³, the mice were used for the following in vivoexperiments.

Pharmacokinetics Study

Healthy male BALB/c mice were randomly divided into three groups (n=3)and given an intravenous injection of either (i) free DY647-labelled GL3siRNA, (ii) DY647-labelled GL3 siRNA-loaded NPs, or (iii) DY647-labelledGL3 siRNA-loaded iRGD-NP at 650 μg siRNA dose per kg mouse weight. Atpredetermined time intervals, orbital vein blood (20 μL) was withdrawnusing a tube containing heparin, and the wound was pressed for severalseconds to stop the bleeding. The fluorescence intensity ofDY647-labelled siRNA in the blood was determined by microplate reader.The blood circulation half-life (t1/2) was calculated by first-orderdecay fit.

Biodistribution

PC3 tumor-bearing male BALB/c nude mice were randomly divided into threegroups (n=3) and given an intravenous injection of either (i) freeDY677-labelled GL3 siRNA, (ii) DY677-labelled GL3 siRNA-loaded NPs or(iii) DY677-labelled GL3 siRNA-loaded iRGD-NPs at 650 μg siRNA dose perkg mouse weight. Twenty-four hours after the injection, the mice wereimaged using the Maestro 2 In-Vivo Imaging System (Cri Inc). Organs andtumors were then harvested and imaged. To quantify the accumulation ofNPs in tumors and organs, the fluorescence intensity of each tissue wasquantified by Image-J.

Immunofluorescence Staining

PC3 tumor-bearing male BALB/c nude mice were randomly divided into threegroups (n=3) and intravenously injected with either (i) freeDY677-labelled GL3 siRNA, (ii) DY677-labelled GL3 siRNA-loaded NPs or(iii) DY677-labelled GL3 siRNA-loaded iRGD-NPs at 650 μg siRNA dose perkg mouse weight. Four hours after injection, the mice were sacrificedand the tumors were harvested, followed by fixing with 4%paraformaldehyde, embedding in paraffin, and cutting into sections. Toimage the tumor vasculature, the slices were heated at 60° C. for 1 hand washed with xylene, ethanol, and PBS thrice. After blocking with 10%FBS for 1.5 h, the slices were incubated with rat anti-mouse CD31antibody (Abcam) at 4° C. for 1 h. After washing with PBS/0.2% tritonX-100 thrice, Alexa Flour 488-conjugated secondary antibody (Goatanti-rat IgG, Abcam) was added for 1 h to stain the slices. Thereafter,the slices were washed with PBS thrice and then stained with Hoechst33342. The images of the tumor vasculature were viewed on a FLV1000CLSM.

In Vivo Survivin Silencing

PC3 tumor-bearing male BALB/c nude mice were randomly divided into twogroups (n=3) and intravenously injected with (i) survivin siRNA-loadedNPs or (ii) survivin siRNA-loaded iRGD-NPs for three consecutive days.Twenty-four hours after the final injection, mice were sacrificed andtumors were harvested. The proteins in the tumor were extracted usingmodified radioimmunoprecipitation assay lysis buffer (50 mM Tris-HCl pH7.4, 150 mM NaCl, 1% NP-40 substitute, 0.25% sodium deoxycholate, 1 mMsodium fluoride, 1 mM Na₃VO₄, 1 mM EDTA), supplemented with proteaseinhibitor cocktail and 1 mM phenylmethanesulfonyl fluoride (PMSF). Theexpression of survivin was examined using the aforementioned westernblot analysis.

Inhibition of Tumor Growth

PC3 tumor-bearing male BALB/c nude mice were randomly divided into fourgroups (n=5) and intravenously injected with (i) PBS, (ii) GL3siRNA-loaded NPs, (iii) survivin siRNA-loaded NPs or (iv) survivinsiRNA-loaded iRGD-NPs at 650 μg siRNA dose per kg mouse weight onceevery two days. All the mice were administrated by administered fiveconsecutive injections and the tumor growth was monitored every two daysby measuring perpendicular diameters using a caliper and tumor volumewas calculated as follows:

V=W ² ×L/2

where W and L are the shortest and longest diameters, respectively.

Histology

Healthy male BALB/c mice were randomly divided into three groups (n=3)and administered daily intravenous injections of either (i) PBS, (ii)survivin siRNA-loaded NPs or (iii) survivin siRNA-loaded iRGD-NPs at 650siRNA dose per kg mouse weight. After three consecutive injections, themain organs were collected 2 days post the final injection, fixed with4% paraformaldehyde, and embedded in paraffin. Tissue sections werestained with H&E and viewed under optical microscope.

Results

A long-circulating, optionally cell-penetrating, and stimuli-responsiveNP platform for effective in vivo delivery of therapeutic, prophylacticand/or diagnostic agents is made of an amphiphilic polymer, mostpreferably a PEGylated polymer, which shows a response to a stimulussuch as pH, temperature, or light, such as an ultra pH-responsivecharacteristic with a pKa close to the endosomal pH (6.0-6.5) (Wang Y etal, Nat Mater, 13, 204-212 (2014)). The polymer may include a targetingor cell penetrating or adhesion molecule such as a tumor-penetratingpeptide iRGD (FIGS. 1A-1B).

As demonstrated by example 1, after encapsulating the agent(s) to bedelivered, the resulting delivery system shows four unique features(FIG. 1C):

i) the surface-encoded iRGD peptide endows the NPs with tumor-targetingand tumor-penetrating abilities;

ii) the hydrophilic PEG shells prolong the blood circulation;

iii) a small population of cationic lipid-like grafts randomly dispersedin the hydrophobic poly(2-(diisopropylamino) ethylmethacrylate) (PDPA)segment can entrap siRNA in the hydrophobic cores of the NPs; and iv)the rapid protonation of the ultra pH-responsive PDPA segment inducesthe endosomal swelling via the “proton sponge” effect, which synergizeswith the insertion of the cationic lipid-like grafts into endosomalmembrane to induce membrane destabilization (Zhu X et al., Proceedingsof the National Academy of Sciences, 112, 7779-7784 (2015)) andefficient endosomal escape.

The amphiphilic polymer, methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidyl methacrylate)(Meo-PEG-b-P(DPA-co-GMA)) was first synthesized (Table 1), which wasfurther grafted by tetraethylenepentamine (TEPA) and 1,2-epoxyhexadecaneto obtain Meo-PEG-b-P(DPA-co-GMA-TEPA-C14).

Synthesis Scheme of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)

The length of PDPA segment was varied to adjust siRNA encapsulationefficiency (EE %). As the PDPA length increases, the EE % and size ofthe resulting NPs increase (Table 3), possibly because the increasedPDPA length leads to an increase in the size of the hydrophobic core.Specifically, the EE % reaches almost 100% for the polymer with 80(PDPA80) or 100 (PDPA100) DPA repeat units. Notably, using a mixture ofMeo-PEG-b-P(DPA-co-GMA-TEPA-C14) (90 mol %) and tumor-penetratingpolymer (iRGD-PEG-b-PDPA, 10 mol %, FIG. 1A) to prepare NPs does notcause obvious change in the EE % or particle size (Table 4).

TABLE 3 Size, zeta potential, siRNA encapsulation efficiency (EE %), andpH responsiveness of the NPs prepared fromMeo-PEG-b-P(DPA-co-GMA-TEPA-C14) Polymer DPA repeating pKa of Size Zetapotential ΔpH No. abbreviation units a polymer b (nm) c (mv) EE % d10%-90% NPs40 PDPA40 39 6.34 62.5 4.79 54.6 0.45 NPs50 PDPA50 50 6.3169.6 5.26 59.6 0.40 NPs60 PDPA60 58 6.29 75.9 3.13 65.6 0.37 NPs70PDPA70 69 6.26 66.0 6.44 69.7 0.35 NPs80 PDPA80 80 6.24 69.7 3.81 99.70.34 NPs100 PDPA100 99 6.21 82.3 9.26 100 0.33 a Determined by ¹HNMRshown in Table 1. b Determined by acid-base titration c Determined bydynamic light scattering (DLS). d DY547-labelled GL3 siRNA was used toexamine the EE %.

The polymer, PDPA80 (pKa 6.24, Table 3), was chosen for pH responseevaluation by incorporating a near-infrared dye, Cy5.5, into its PDPAsegment. Due to the quenching of the aggregated fluorophores inside thehydrophobic cores of the NPs (Wang Y et al, Nat Mater, 13, 204-212(2014)), there is no fluorescence signal at a pH above pKa of PDPA80. Incontrast, at a pH below pKa, the protonated PDPA segment induces thedisassembly of the NPs and a dramatic increase in the fluorescencesignal. Measurement of the fluorescence intensity as a function of pHfor the Cy.5.5-labelled NPs of PDPA80 reveals that the pH differencefrom 10 to 90% fluorescence activation (ΔpH10-90%) is 0.34 (FIG. 2A andTable 3) (Wang Y et al, Nat Mater, 13, 204-212 (2014)), which is muchsmaller than that of small molecule dyes (about 2 pH units) (Urano Y etal., Nat Med, 15, 104-109 (2009)), indicating the ultra-fast pH responseof PDPA80. This characteristic is confirmed by transmission electronmicroscope (TEM). The spherical siRNA-loaded NPs could be visualized ata pH of 6.5, with an average size of 69.7 nm determined by dynamic lightscattering (DLS, Table 3). If altering pH to 6.0, there are noobservable NPs after 20 min incubation. With this morphological change,the NPs offer super-fast release of DY547-labelled GL3 siRNA(DY547-siRNA) (FIG. 2B). Around 90% loaded siRNA has been releasedwithin 4 h at a pH of 6.0. Within the same time frame, less than 30% ofthe loaded siRNA is released at a pH of 7.4.

TABLE 4 Size, zeta potential and siRNA encapsulation efficiency (EE %)of the iRGD-NPs of prepared from the mixture of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) and iRGD-PEG-b-PDPA a No. Size (nm) b Zeta potential (mv)EE % c iRGD-NPs₄₀ 64.2 3.26 55.1 iRGD-NPs₅₀ 68.3 3.98 59.7 iRGD-NPs₆₀82.1 5.69 66.4 iRGD-NPs₇₀ 76.5 7.18 69.6 iRGD-NPs₈₀ 70.7 5.26 99.8iRGD-NPs₁₀₀ 86.3 8.93 100 a The molar ratio ofMeo-PEG-b-P(DPA-co-GMA-TEPA-C14) and iRGD-PEG-b-PDPA is 9:1. bDetermined by dynamic light scattering (DLS). c DY547-labelled GL3 siRNAwas used to examine the EE%.

Luciferase-expressing HeLa (Luc-HeLa) cells were used to evaluate thegene silencing efficacy. GL3 siRNA was employed to suppress luciferaseexpression. All the siRNA-loaded NPs show a reduction in luciferaseexpression at a 10 nM siRNA dose (FIG. 3A), with the differentialsilencing efficacy depending upon the polymer structure. In comparison,the NPs with iRGD peptide (denoted iRGD-NPs) offer much better genesilencing efficacy. In particular, the iRGD-NPs₈₀ prepared from PDPA80show the best gene silencing efficacy, i.e., >90% knockdown inluciferase expression without obvious cytotoxicity (FIG. 4). Cellviability of Luc-HeLa cells in the presence of 10 nM siRNA dose of theGL3 siRNA-loaded NPs formed with PDPA40, PDPA50, PDPA60, PDPA70, PDPA80,or PDPA100; and Lipo2K-GL3 siRNA complex was compared to cells incubatedwith free medium. No obvious cytotoxicity was observed with these NPs(FIG. 4).

After acquiring the nanoplatform with optimal silencing efficacy(iRGD-NPs₈₀), flow cytometry was employed to evaluate its in vitrotumor-targeting ability. With the specific recognition between integrins(α_(v)β₃ and α_(v)β₅, FIGS. 5A-5D) on Luc-HeLa cells and iRGD, theuptake of DY547-siRNA-loaded iRGD-NPs₈₀ is more than 3-fold higher thanthat of iRGD-absent NPs₈₀ (FIGS. 3B and 6A-6C), demonstrating theexcellent tumor-targeting ability of iRGD-NPs₈₀. Endosomal escapeability was assessed by staining the endosomes with lysotracker green.Fluorescent image of Luc-HeLa cells incubated with the siRNA-loadediRGD-NPs₈₀ showed that a majority of the internalized siRNA-loaded NPsentered the cytoplasm after 4 h incubation, indicating the effectiveendosomal escape of the iRGD-NPs₈₀. In comparison, for the iRGD-NPsprepared from polymer without lipid-like grafts or pH response (FIGS.7A-7D), the endosome escape ability is relatively weaker, thus leadingto a much lower silencing efficacy (FIGS. 7A-7B).

The iRGD-NPs80 was further tested on whether it can downregulatesurvivin expression, an inhibitor of apoptosis protein that isover-expressed in most cancers (Altieri D C et al., Nat Rev Cancer, 3,46-54 (2003)). PC3 cells, a prostate cancer cell line showing targeteduptake of iRGD-NPs (FIGS. 5A-5D and 6A-6C) where the uptake ofDY547-siRNA-loaded iRGD-NPs₈₀ is also about 3-fold higher than that ofiRGD-absent NPs₈₀, were used as a model cell line. Western blot analysiswas carried out for determining survivin expression in PC3 cells treatedby survivin siRNA-loaded NPs₈₀ or survivin siRNA-loaded iRGD-NPs₈₀. Thewestern blot analysis indicates that the survivin siRNA-loadediRGD-NPs₈₀ significantly suppress survivin expression (>80% knockdown)at a 10 nM siRNA dose. At a 50 nM siRNA dose, survivin expression isnearly absent (<3%, FIG. 7C). The similar result can be also found inthe immunofluorescence staining analysis of PC3 cells treated bysurvivin siRNA-loaded NPs₈₀ or survivin siRNA-loaded iRGD-NPs₈₀ at a 10nM siRNA dose. Very weak red fluorescence corresponding to the residualsurvivin can be observed in the cells treated with iRGD-NPs₈₀ at a 10 nMsiRNA dose. With such suppressed survivin expression, the proliferationrate of PC3 cells is very slow. There is only 2.5-fold increase in cellnumber after 8 days incubation (FIG. 3D).

After validating the efficient gene silencing of iRGD-NPs₈₀, their invivo tumor-targeting ability was assessed. Pharmacokinetics was firstexamined by intravenous injection of DY647-siRNA-loaded NPs. As shown inFIG. 15A, the blood half-life (t_(1/2)) of iRGD-NPs₈₀ is around 3.56 h,which is far longer than that of naked siRNA (t_(1/2)<10 min). Thisprolonged blood circulation is mainly due to the protection of PEG outerlayer and small particle size (Knop K et al., Angewandte ChemieInternational Edition, 49, 6288-6308(2010)). The in vivo tumor-targetingability was evaluated by intravenously injecting DY677-siRNA-loaded NPsinto PC3 xenograft tumor-bearing mice. Overlaid fluorescent image of PC3xenograft tumor-bearing mice at 24 h post-injection of naked siRNA andsiRNA-loaded NPs showed that, with the iRGD-mediated tumor-targeting,the iRGD-NPs₈₀ show a much higher tumor accumulation than that of NPs₈₀at 24 h post-injection. The tumors and main organs were harvested andthe biodistribution is shown in FIG. 8B. Naked siRNA has acharacteristic biodistribution, i.e., high accumulation in kidney butextremely low accumulation in tumor. With the specific recognitionbetween iRGD and integrins α_(v)β₃ and α_(v)β₅ over-expressed on tumorcells and angiogenic tumor vasculature (Wang Y et al., Nat Mater, 13,204-212 (2014); Sugahara K N et al., Cancer Cell, 16, 510-520(2009)),the tumor accumulation of the iRGD-NPs₈₀ is around 3-fold higher that ofNPs₈₀.

To evaluate the tumor-penetrating ability of the iRGD-NPs₈₀, the tumorswere collected at 4 h post-injection of the DY677-siRNA-loaded NPs andthen sectioned for immunofluorescence staining. There is nearly no nakedsiRNA in the tumor section. For the NPs₈₀, the number of NPs in tumorsection is very low. Additionally, most of these NPs are positioned inthe tumor vessels, and only a small number reach the extravascular tumorparenchyma. In contrast, highly concentrated iRGD-NPs₈₀ with bright redfluorescence could be visualized in the tumor section. Remarkably, amajority of these NPs can cross tumor vessels and reach theextravascular tumor parenchyma, strongly demonstrating the deeptumor-penetrating characteristic of iRGD-NPs₈₀.

Finally, the in vivo inhibition of survivin expression and anti-cancerefficacy was evaluated. The survivin siRNA-loaded NPs were intravenouslyinjected into the PC3 xenograft tumor-bearing mice (650 μg/kg siRNAdose, n=3) for three consecutive days. Western blot analysis of survivinexpression in the PC3 tumor tissue after systemic treatment by controlNPs (GL3 siRNA-loaded NPs₈₀), survivin siRNA-loaded NPs and survivinsiRNA-loaded iRGD-NPs₈₀ showed that the siRNA-loaded NPs indeedsuppressed survivin expression in tumor. In particular, theadministration of survivin siRNA-loaded iRGD-NP₈₀ induces more than 60%knockdown in survivin expression, whereas survivin siRNA-loaded NPsinduced about 25% knockdown in survivin expression (FIG. 9). Thus,survivin siRNA-loaded iRGD-NPs₈₀ showed around 3-fold greater knockdownin survivin expression than that of NPs₈₀. Notably, the administrationof NPs shows negligible in vivo side effects. To confirm whether theNP-mediated survivin silencing has an anti-cancer effect, the survivinsiRNA-loaded NPs were intravenously injected to the mice once every twodays at a 650 μg/kg siRNA dose (n=5). After five consecutive injections(FIG. 10), the tumor growth is inhibited compared to the mice treatedwith PBS or GL3 siRNA-loaded NPs (Control NPs). Harvested PC3 tumor fromeach group at day 16 was compared with GL3 siRNA-loaded NPs₈₀ as acontrol. Particularly, with the excellent tumor-targeting andpenetrating abilities, the iRGD-NPs₈₀ can significantly suppress tumorgrowth, and there is only around 2-fold increase in tumor size at day24. The PC3 xenograft tumor-bearing nude mice treated with PBS, GL3siRNA-loaded NPs₈₀ (Control NPs), or survivin siRNA-loaded NPs₈₀ andiRGD-NPs₈₀ were monitored for body weight but no significant differencewas noticed (FIG. 11).

In summary, an ultra pH-responsive and tumor-penetrating nanoplatformfor targeted systemic siRNA delivery has been developed. The in vitroand in vivo results demonstrate that this polymeric NP has a long bloodcirculation, and can efficiently target tumor and penetrate tumorparenchyma, leading to efficient gene silencing and tumor growthinhibition. The polymeric nanoplatform reported herein may represent arobust siRNA delivery vehicle for the treatment of a myriad of importantdiseases including cancer.

Example 2: Ultra pH-Responsive and Tumor-Penetrating Nanoplatform forTargeted siRNA Delivery with Robust Anti-Cancer Efficacy Methods andMaterials

Materials

Methoxyl-polyethylene glycol (Meo-PEG₁₁₃-OH) and hydroxyl polyethyleneglycol carboxylic acid (HO-PEG₁₁₃-COOH) were purchased from JenKemTechnology and used as received. Oligoarginine (NH2-Rn—CONH2, n=6, 8,10, 20, 30) was provided by MIT Biopolymer facility. Allyl protectedS,S-2-[3-[5-amino-1-carboxypentyl]-ureido]-pentanedioic acid (ACUPA) waskindly provided by BIND Therapeutics as a gift. 2-(Diisopropyl amino)ethyl methacrylate (DPA-MA) and glycidyl methacrylate (GMA) wereprovided by Sigma-Aldrich and passed over an alumina column before usein order to remove the hydroquinone inhibitors. α-Bromoisobutyrylbromide, N,N′-dimethylformamide (DMF), triethylamine (TEA),N,N,N′,N′,N′-pentamethyldiethylenetriamine (PMDETA), copper (I) bromide(CuBr), tetraethylenepentamine (TEPA), isopropyl alcohol,p-toluenesulfinate tetrahydrate (PTSF), tetrakis(triphenylphosphine)palladium (Pd(PPh₃)₄) and dichloromethane (DCM) were acquired fromSigma-Aldrich and used directly. Lipofectamine 2000 (Lipo2K) waspurchased from Invitrogen. Steady-Glo luciferase assay system wasprovided by Promega. GL3, fluorescent dye (DY547, DY647 and Cy5.5)labeled GL3 and PHB1 siRNAs were acquired from Dharmacon. The siRNAsequences are as follows: GL3 siRNA, 5′-CUU ACG CUG AGU ACU UCG AdTdT-3′(sense) (SEQ ID NO:1) and 5′-UCG AAG UAC UCA GCG UAA GdTdT-3′(antisense) (SEQ ID NO:2); PHB1 siRNA, 5′-GCG ACG ACC UUA CAG AGC GUU-3′(sense) (SEQ ID NO:5) and 5′-CGC UCU GUA AGG UCG UCG CUU-3′ (antisense)(SEQ ID NO:6). The fluorescent dyes DY-547 and DY-647 were labeled atthe 5′-end of the sense strand of GL3 siRNA. Cy5.5 was labeled at the5′-end of both the sense and antisense strands of GL3 siRNA. HeLa cellsstably expressing firefly and Renilla luciferase (Luc-HeLa) wereobtained from Alnylam Pharmaceuticals, Inc. The cells were incubated inRPMI 1640 medium (Invitrogen) with 10% fetal bovine serum (FBS,Sigma-Aldrich). All other reagents and solvents are of analytical gradeand used without further purification.

Synthesis of Meo-PEG-Br and Br-PEG-COOH

Meo-PEG₁₁₃-OH (8 g, 1.6 mmol) and TEA (1.3 mL, 9.6 mmol) were dissolvedin 250 mL of DCM. In an ice-salt bath, α-bromoisobutyryl bromide (1 mL,8 mmol) dissolved in 10 mL of DCM was added dropwise. After stirring for24 h, the mixture was washed with 1 M NaOH (3×50 mL), 1 M HCl (3×50 mL),and deionized water (3×50 mL). After drying over anhydrous MgSO₄, thesolution was concentrated, and cold ether was added to precipitate theproduct. After re-precipitating thrice, the product was collected aswhite powder after drying under vacuum. The synthesis of Br-PEG-COOH wascarried out according to a method similar to that described above, bychanging Meo-PEG₁₁₃-OH with HO-PEG₁₁₃-COOH. The synthesis scheme ofMeo-PEG-Br is shown below.

Synthesis of methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate) (Meo-PEG-b-P(DPA-co-GMA))

Meo-PEG-b-P(DPA-co-GMA) copolymer was synthesized by atom transferradical polymerization (ATRP). DPA-MA (2.6 g, 12 mmol), GMA (0.07 g,0.45 mmol), Meo-PEG-Br (0.75 g, 0.15 mmol), and PMDETA (31.5 μL, 0.15mmol) were added to a polymerization tube. DMF (3 mL) and 2-propanol (3mL) were then added to dissolve the monomer and initiator. After threecycles of freeze-pump-thaw to remove oxygen, CuBr (21.6 mg, 0.15 mmol)was added under nitrogen atmosphere and the polymerization tube wassealed under vacuum. After polymerization at 40° C. for 24 h,tetrahydrofuran (THF) was added to dilute the product, which was thenpassed through a neutral Al₂O₃ column to remove the catalyst. Theresulting THF solution was concentrated and the residue was dialyzedagainst THF, followed by deionized water. The expected copolymer wascollected as a white powder after freeze-drying under vacuum. Thesynthesis scheme is shown below.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-Rn)

Meo-PEG-b-P(DPA-co-GMA-Rn) was synthesized via the ring opening reactionbetween the amino group of NH₂—Rn—CONH₂ and the epoxy group of the GMArepeating unit. In brief, Meo-PEG-b-P(DPA-co-GMA) (1 g) dissolved in DMF(15 mL) was added dropwise to the DMF solution (10 mL) of NH₂—Rn—CONH₂(10-fold molar excess relative to the GMA repeating unit). Afterreaction at 60° C. for 7 h, the mixture was transferred to a dialysistube and then dialyzed against deionized water. TheMeo-PEG-b-P(DPA-co-GMA-Rn) was finally collected as a white powder afterfreeze-drying under vacuum.

The synthesis route of Meo-PEG-b-P(DPA-co-GMA-Rn) is shown below.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA)

Meo-PEG-b-P(DPA-co-GMA-TEPA) was synthesized via the ring openingreaction between TEPA and the epoxy group of the GMA repeating unit. Inbrief, Meo-PEG-b-P(DPA-co-GMA) (1 g) dissolved in DMF (15 mL) was addeddropwise to the DMF solution (5 mL) of TEPA (30-fold molar excessrelative to the GMA repeating unit). After reacting at 60° C. for 7 h,the mixture was transferred to a dialysis tube and then dialyzed againstdeionized water. The Meo-PEG-b-P(DPA-co-GMA-TEPA) was finally collectedas a white powder after freeze-drying under vacuum. The synthesis routeof Meo-PEG-b-P(DPA-co-GMA-TEPA) is shown below.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5)

Meo-PEG-b-P(DPA-co-GMA-TEPA) (0.2 g) and Cy5.5 NHS ester (1.5-fold molarexcess relative to the TEPA repeating unit) were well dissolved in 5 mLof THF. After constantly stirring in dark for 48 h, the solution wasdialyzed against deionized water and the product was collected afterfreeze-drying.

The synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5) is shown below.

Synthesis of HOOC-PEG-b-PDPA

HOOC-PEG-b-PDPA copolymers were also synthesized by the ATRP method. Forexample, DPA-MA (1.73 g, 8 mmol), Br-PEG-COOH (0.5 g, 0.1 mmol), andPMDETA (21 μL, 0.1 mmol) were added to a polymerization tube.Subsequently, DMF (2 mL) and 2-propanol (2 mL) were added to dissolvethe monomer and initiator. After three cycles of freeze-pump-thaw toremove oxygen, CuBr (14.4 mg, 0.1 mmol) was added under nitrogenatmosphere and the polymerization tube was sealed under vacuum. Afterpolymerization at 40° C. for 24 h, tetrahydrofuran (THF) was added todilute the product, which was then passed through a neutral Al₂O₃ columnto remove the catalyst. The obtained THF solution was concentrated andthe residue was dialyzed against deionized water. The HOOC-PEG-b-PDPAwas obtained as a white powder after freeze-drying under vacuum. Thesynthesis route of HOOC-PEG-b-PDPA is shown below.

Synthesis of Allyl-protected ACUPA-PEG-b-PDPA

HOOC-PEG-b-PDPA copolymer (1 g), allyl protected ACUPA (5-fold molarexcess relative to the terminal carboxylic acid group), EDC.HCl (3-foldmolar excess relative to the terminal carboxylic acid group), and NHS(3-fold molar excess relative to the terminal carboxylic acid group)were well dissolved in 15 mL of THF. The mixture was stirred at roomtemperature for 48 h. The solution was subsequently dialyzed against DMFfor 48 h followed by deionized water. The expected allyl-protectedACUPA-PEG-PDPA was collected after freeze-drying. The synthesis route ofAllyl-protected ACUPA-PEG-b-PDPA is shown below.

Synthesis of ACUPA-PEG-b-PDPA

Allyl-protected ACUPA-PEG-PDPA (1 g) was well dissolved in 15 mL of THFand Pd(PPh₃)₄ (42 mg) was added. Under stirring, PTSF (155 mg) dissolvedin 2.5 mL of methanol was added to the suspension of Allyl protectedACUPA-PEG-PDPA and Pd(PPh₃)₄. After reacting in dark for 2 h, thesuspension was transferred to a dialysis tube (MWCO 3500) and dialyzedagainst toluene for 48 h. Thereafter, the solution was removed by rotaryevaporation and the residue was dissolved in 15 mL of THF. Afterdialyzing against deionized water for 48 h, the ACUPA-PEG-PDPA wascollected through freeze-drying.

The synthesis route of ACUPA-PEG-b-PDPA is shown below.

Gel Permeation Chromatography (GPC)

Number- and weight-average molecular weights (Mn and Mw, respectively)of the polymers were determined by a gel permeation chromatographicsystem equipped with a Waters 2690D separations module and a Waters 2410refractive index detector. THF was used as the eluent at a flow rate of0.3 mL/min. Waters millennium module software was used to calculatemolecular weight on the basis of a universal calibration curve generatedby polystyrene standard of narrow molecular weight distribution.

¹H Nuclear Magnetic Resonance (¹HNMR)

The ¹HNMR spectra of the polymers were recorded on a Mercury VX-300spectrometer at 400 MHz (Varian, USA), using CDCl₃ as a solvent and TMSas an internal standard.

Acid-Base Titration

Meo-PEG-b-P(DPA-co-GMA-Rn) was dispersed in deionized water, and aconcentrated HCl aqueous solution was added until the copolymer wascompletely dissolved (1 mg/mL). Subsequently, 1 M NaOH aqueous solutionwas added in 1-5 μL increments. After each addition, the solution wasconstantly stirred for 3 min, and the solution pH was measured using apH meter. The pKa of the copolymer was determined as the pH at which 50%of the copolymer turns ionizes.

Preparation and Characterization of Nanoparticles (NPs)

Meo-PEG-b-P(DPA-co-GMA-Rn) was dissolved in THF to form a homogenoussolution with a concentration of 4 mg/mL. Subsequently, a certain volumeof this THF solution was taken and mixed with 1 nmol siRNA (0.1 nmol/4aqueous solution) in an N/P molar ratio of 80:1. Under vigorouslystirring (1000 rpm), the mixture was added dropwise to 4 mL of deionizedwater. The NP dispersion formed was transferred to an ultrafiltrationdevice (EMD Millipore, MWCO 100 K) and centrifuged to remove the organicsolvent and free compounds. After washing with PBS (pH 7.4) solution(3×5 mL), the siRNA loaded NPs were dispersed in 1 mL of phosphatebuffered saline (PBS, pH 7.4) solution. Size and zeta potential weredetermined by dynamic light scattering (DLS, Brookhaven InstrumentsCorporation). The morphology of NPs was visualized on a Tecnai G2 SpiritBioTWIN transmission electron microscope (TEM). Before observation, thesample was stained with 1% uranyl acetate and dried under air. Todetermine the siRNA encapsulation efficiency, DY547-labelled GL3 siRNA(DY547-siRNA) loaded NPs were prepared according to the method describedabove. A small volume (50 μL) of the NP solution was withdrawn and mixedwith 20-fold DMSO. The fluorescence intensity of DY547-siRNA wasmeasured using a Synergy HT multi-mode microplate reader (BioTekInstruments) and compared to the free DY-547 labelled GL3 siRNA solution(1 nmol/mL PBS solution.)

To prepare the ACUPA-NPs, Meo-PEG-b-P(DPA-co-GMA-Rn) (4 mg/mL in THF)was mixed with 1 nmol siRNA (0.1 nmol/4 aqueous solution) in a N/P molarratio of 80:1. Then ACUPA-PEG-b-PDPA (4 mg/mL in THF, 10 mol % comparedto Meo-PEG-b-P(DPA-co-GMA-Rn)) was added, and the mixture was addeddropwise to 4 mL of deionized water. The ACUPA-NPs were purified by anultrafiltration device (EMD Millipore, MWCO 100 K) and finally dispersedin 1 mL of PBS. The siRNA encapsulation efficiency was examined byreplacing the siRNA with DY-547 labelled GL3 siRNA.

Evaluation of pH Sensitivity

The THF solution of Meo-PEG-b-P(DPA-co-GMA-Rn) (4 mg/mL) andMeo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5) (4 mg/mL) was mixed in a volume ratioof 8:2. Under vigorously stirring (1000 rpm), 0.2 mL of the mixture wasadded dropwise to 2 mL of deionized water. After collection andpurification by an ultrafiltration device (EMD Millipore, MWCO 100 kDa),the NPs formed were dispersed in 1 mL of deionized water. Subsequently,1 M NaOH or HCl was added in 1-5 μL increments, and the fluorescenceintensity of the NPs was measured on a Synergy HT multi-mode microplatereader. The normalized fluorescence intensity (NFI) vs. pH profile wasused to quantitatively assess the pH responsiveness. NFI is calculatedas follows:

NFI=(F−Fmin)/(Fmax−Fmin)

where F is the fluorescence intensity of the NPs at any given pH valueand Fmax and Fmin are the maximal and minimal fluorescence intensity ofthe NPs, respectively.

In Vitro siRNA Release

DY547-siRNA-loaded NPs were prepared as described above. Subsequently,the NPs were dispersed in 1 mL of PBS (pH 7.4) and then transferred to aFloat-a-lyzer G2 dialysis device (MWCO 100 kDa, Spectrum) that wasimmersed in PBS (pH 7.4) at 37° C. At a predetermined interval, 5 μL ofthe NP solution was withdrawn and mixed with 20-fold DMSO. Thefluorescence intensity of DY547-siRNA was determined by Synergy HTmulti-mode microplate reader.

Cell Culture

Human cervical cancer cell line with the expression of luciferase(Luc-HeLa) and prostate cancer (PCa) cell lines (LNCaP, PC3, DU145,22RV1) were incubated in RPMI 1640 medium with 10% FBS at 37° C. in ahumidified atmosphere containing 5% CO₂.

Luciferase Silencing

Luc-HeLa cells were seeded in 96-well plates (5,000 cells per well) andincubated in 0.1 mL of RPMI 1640 medium with 10% FBS for 24 h.Thereafter, the GL3 siRNA-loaded NPs were added. After incubating for 24h, the cells were washed with fresh medium and allowed to incubate foranother 48 h. The expression of firefly luciferase in HeLa cells wasdetermined using Steady-Glo luciferase assay kits. Cytotoxicity wasmeasured using the alamarBlue assay according to the manufacturer'sprotocol. The luminescence or fluorescence intensity was measured usinga microplate reader, and the average value of five independentexperiments was collected. As a control, the silencing effect ofLipo2K/GL3 siRNA complexes was also evaluated according to the proceduredescribed above and compared to that of GL3 siRNA-loaded NPs.

Determination of the Expression of Prostate Specific Membrane Antigen(PSMA)

The PCa cell lines were seeded in 6-well plates (50,000 cells per well)and incubated in 1 mL of RPMI 1640 medium containing 10% FBS for 24 h.Thereafter, 10 μL of PE-conjugated anti-human PSMA antibody (BioLegend)was added, and the cells were allowed to incubate for another 4 h. Afterremoving the medium and washing with PBS (pH 7.4) solution thrice, thecells were collected for flow cytometry quantitative analysis (DXP11Analyzer).

Evaluation of Endosomal Escape

Luc-HeLa cells (20,000 cells) were seeded in discs and incubated in 1 mLof RPMI 1640 medium containing 10% FBS for 24 h. Subsequently, theDY547-siRNA-loaded NPs were added, and the cells were allowed toincubate for 1 or 2 h. After removing the medium and subsequentlywashing with PBS (pH 7.4) solution thrice, the endosomes and nuclei werestained with lysotracker green and Hoechst 33342, respectively. Thecells were then viewed under a FV1000 confocal laser scanning microscope(CLSM, Olympus).

Flow Cytometry

Luc-HeLa and PCa cell lines (LNCaP, PC3, DU145) were seeded in 6-wellplates (50,000 cells per well) and incubated in 1 mL of RPMI 1640 mediumcontaining 10% FBS for 24 h. Subsequently, the DY547-siRNA-loaded NPs orACUPA-NPs were added, and the cells were allowed to incubate for another4 h. After removing the medium and subsequently washing with PBS (pH7.4) solution thrice, the cells were collected for flow cytometryquantitative analysis.

In Vitro PHB1 Silencing

LNCaP cells were seeded in 6-well plates (50,000 cells per well) andincubated in 1 mL of RPMI 1640 medium containing 10% FBS for 24 h.Subsequently, the cells were transfected with the PHB1 siRNA-loaded NPsor ACUPA-NPs for 24 h. After washing the cells with PBS thrice, thecells were further incubated in fresh medium for another 48 h.Thereafter, the cells were digested by trypsin and the proteins wereextracted using modified radioimmunoprecipitation assay lysis buffer (50mM Tris-HCl pH 7.4, 150 mM NaCl, 1% NP-40 substitute, 0.25% sodiumdeoxycholate, 1 mM sodium fluoride, 1 mM Na3VO4, 1 mM EDTA),supplemented with protease inhibitor cocktail and 1 mMphenylmethanesulfonyl fluoride (PMSF). The expression of PHB1 wasexamined using the following western blot analysis.

Western Blot Analysis

Equal amounts of protein, as determined with a bicinchoninic acid (BCA)protein assay kit (Pierce/Thermo Scientific) according to themanufacturer's instructions, were added to SDS-PAGE gels and separatedby gel electrophoresis. After transferring the proteins from gel topolyvinylidene difluoride membrane, the blots were blocked with 3% BSAin TBST (50 mM Tris-HCl pH 7.4, 150 mM NaCl, and 0.1% Tween 20) and thenincubated with a mixture of PHB1 rabbit antibody (Cell Signaling) andβ-actin rabbit antibody (Cell Signaling). The expression of PHB1 wasdetected with horseradish peroxidase (HRP)-conjugated secondary antibody(anti-rabbit IgG HRP-linked antibody, Cell Signaling) and an enhancedchemiluminescence (ECL) detection system (Pierce).

In Vitro Cell Proliferation

LNCaP cells were seeded in 6-well plates (20,000 cells per well) andincubated in 1 mL of RPMI 1640 medium containing 10% FBS for 24 h.Thereafter, the cells were transfected with the PHB1 siRNA-loaded NPs orACUPA-NPs for 24 h and then washed with fresh medium for furtherincubation. At predetermined intervals, the cytotoxicity was measuredusing the alamarBlue assay according to the manufacturer's protocol.After each measurement, the alamarBlue agent was removed and the cellswere incubated in fresh medium for further proliferation.

LNCaP Xenograft Tumor Model

The tumor model was constructed by subcutaneous injection with 200 μl ofLNCaP cell suspension (a mixture of RPMI 1640 medium and Matrigel in 1:1volume ratio) with a density of 3×10⁷ cells/mL into the back region ofhealthy male BALB/c nude mice. When the volume of the PC3 tumorxenograft reached ˜50 mm³, the mice were used for the following in vivoexperiments.

Pharmacokinetics Study

Healthy male BALB/c mice were randomly divided into three groups (n=3)and given an intravenous injection of either (i) free DY647-labelled GL3siRNA (DY647-siRNA), (ii) DY647-siRNA-loaded NPs, or (iii)DY647-siRNA-loaded ACUPA-NPs at a 650 μg/kg siRNA dose. At predeterminedtime intervals, orbital vein blood (20 μL) was withdrawn using a tubecontaining heparin, and the wound was pressed for several seconds tostop the bleeding. The fluorescence intensity of DY-647 labelled siRNAin the blood was determined using a microplate reader. The bloodcirculation half-life (t1/2) was calculated by first-order decay fit.

Biodistribution

LNCaP tumor-bearing male BALB/c nude mice were randomly divided intofour groups (n=3) and given an intravenous injection of either (i) freeCy5.5-labelled GL3 siRNA (Cy5.5-siRNA), (ii) Cy5.5-siRNA-loaded NPs,(iii) Cy5.5-siRNA-loaded ACUPA-NPs or (iv) PSMA antibody (5 mg/kg dose)15 min followed by Cy5.5-siRNA loaded ACUPA-NPs at a 650 μg/kg siRNAdose. Twenty-four hours after the injection, the mice were imaged usingthe Maestro 2 In-Vivo Imaging System (Cri Inc). Main organs and tumorswere then harvested and imaged. To quantify the accumulation of NPs intumors and organs, the fluorescence intensity of each tissue wasquantified by Image-J.

In Vivo PHB1 Silencing

LNCaP tumor-bearing male BALB/c nude mice were randomly divided into twogroups (n=3) and intravenously injected with (i) PHB1 siRNA-loaded NPsor (ii) PHB1 siRNA-loaded ACUPA-NPs for three consecutive days.Twenty-four hours post the final injection, mice were sacrificed andtumors were harvested. The proteins in the tumor were extracted usingmodified radioimmunoprecipitation assay lysis buffer (50 mM Tris-HCl pH7.4, 150 mM NaCl, 1% NP-40 substitute, 0.25% sodium deoxycholate, 1 mMsodium fluoride, 1 mM Na3VO4, 1 mM EDTA), supplemented with proteaseinhibitor cocktail and 1 mM phenylmethanesulfonyl fluoride (PMSF). Theexpression of PHB1 was examined using the aforementioned western blotanalysis.

Inhibition of Tumor Growth

LNCaP tumor-bearing male BALB/c nude mice were randomly divided intofour groups (n=5) and intravenously injected with (i) PBS, (ii) GL3siRNA-loaded NPs, (iii) PHB1 siRNA-loaded NPs or (iv) PHB1 siRNA-loadedACUPA-NPs at a 650 μg/kg siRNA dose once every two days. All the micewere administrated five consecutive injections and the tumor growth wasmonitored every two days by measuring perpendicular diameters using acaliper and tumor volume was calculated as follows:

V=W ² ×L/2

where W and L are the shortest and longest diameters, respectively.

Histology

Healthy male BALB/c mice were randomly divided into three groups (n=3)and administered daily intravenous injections of either (i) PBS, (ii)PHB1 siRNA-loaded NPs or (iii) PHB1 siRNA-loaded ACUPA-NPs at a 650μg/kg siRNA dose. After five consecutive injections (once every twodays), the main organs were collected 2 days post the final injection,fixed with 4% paraformaldehyde, and embedded in paraffin. Tissuesections were stained with hematoxylin-eosin (H&E) and viewed under anoptical microscope.

Results

A high loading, biosafe and long-circulating siRNA delivery nanoplatformthat shows high prostate specificity and excellent endosomal escapecapability for PCa therapy is developed. To construct this robustnanoplatform, a library of ultra pH-responsive PEGylated polymers weredeveloped, containing membrane-penetrating oligoarginine grafts and anS,S-2-[3-[5-amino-1-carboxypentyl]-ureido]-pentanedioic acid (ACUPA)terminus. ACUPA is a small molecule target ligand that can specificallybind to prostate specific membrane antigen (PSMA), which is abundantlyexpressed in PCa, in both its metastatic form and the hormone-refractoryform (Israeli, R et al., Cancer Research, 53, (2), 227-230 (1993);Murphy, G P et al., Cancer, 83, (11), 2259-2269 (1998); Dhar, S et al.,Proceedings of the National Academy of Sciences, 105, (45), 17356-17361(2008)). The resulting polymer/siRNA nanoassembly is expected to havethe following unique features (FIG. 12): i) the surface-encoded ACUPAmoieties endow the NPs with high PCa specificity and selectivity; ii)the hydrophilic PEG shells allow the NPs to escape immunologicalrecognition, thus improving blood circulation (Knop, K et al.,Angewandte Chemie International Edition, 49, (36), 6288-6308 (2010);Guo, X et al., Accounts of Chemical Research, 45, 971-979 (2012);Bertrand, N et al., Advanced Drug Delivery Reviews, 66, 2-25(2014); iii)a small population of cationic membrane-penetrating oligoarginine graftsrandomly dispersed in the hydrophobic poly(2-(diisopropylamino)ethylmethacrylate) (PDPA) segment can strongly entrap a high amount ofsiRNA into the hydrophobic cores of the NPs; iv) the rapid protonationof the ultra pH-responsive PDPA segment with a pKa close to endosomal pH(6.0-6.5) causes the swelling of endosomes via the “proton sponge”effect (Yu, H et al., ACS Nano, 5, 9246-9255 (2011); Zhou, K et al.,Angewandte Chemie International Edition, 50, 6109-6114 (2011)), whichworks alongside the membrane-penetrating oligoarginine grafts to induceefficient and fast release of siRNA in cytoplasm to inhibit tumor growth(Chen, J X et al., ACS Applied Materials & Interfaces, 6, (1), 593-598(2014); Chen, J X et al., Biomaterials, 32, (6), 1678-1684 (2011); Lim,Y B et al., M. Angewandte Chemie International Edition, 46,9011-9014(2007).

Atom-transfer radical polymerization (ATRP) was employed to synthesizethe PEGlyated polymer, methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidyl methacrylate)(Meo-PEG-b-P(DPA-co-GMA)). The epoxy group was subsequently subjected toattack by oligoarginine (R_(n), n=6, 8, 10, 20, 30) to endow theresulting polymer (Meo-PEG-b-P(DPA-co-GMA-R_(n)) with siRNA loading andendosomal membrane-penetrating abilities. The PCa-specific PEGylatedpolymer, ACUPA-PEG-b-PDPA was also prepared by ATRP, followed byconjugation with ACUPA.

The length of the oligoarginine grafts was varied to adjust the siRNAloading ability and physiochemical properties of the NPs. ThesiRNA-loaded NPs were prepared by mixing siRNA aqueous solution with thetetrahydrofuran (THF) solution of Meo-PEG-b-P(DPA-co-GMA-Rn) at a N/Pmolar ratio of 80:1. The amphiphilic nature of the polymers inducesself-assembly into NPs with siRNA entrapped in the hydrophobic cores. Asthe number of arginine residues increases from 6 to 30, the size of theresulting NPs increases from 56.6 to 189.9 nm (FIG. 13A, Table 5), butsiRNA encapsulation efficiency (EE %) decreases from 90.6% to 49.7%(FIG. 13B). One possible reason is that enhancing overall hydrophilicityof the amphiphilic polymers by increasing the length of theoligoarginine grafts leads to the formation of looser NPs with weakersiRNA loading ability. This also results in an increased zeta potential(FIG. 13B). Notably, there is no obvious change in the EE % or size ofthe NPs made with the mixture of Meo-PEG-b-P(DPA-co-GMA-Rn) (90 mol %)and ACUPA-PEG-b-PDPA (10 mol %) (Table 6).

TABLE 5 Size, zeta potential, siRNA encapsulation efficiency (EE %), andpH responsiveness of the NPs prepared from Meo-PEG-b-P(DPA-co-GMA-Rn)Size Zeta (nm) potential ΔpH10- No. a (mv) EE % b pKa b 90% NPsR6 56.67.09 90.6 6.24 0.32 NPsR8 83.4 8.26 84.4 6.27 0.36 NPsR10 90.8 9.13 72.76.31 0.39 NPsR20 117.8 13.74 54 6.42 0.46 NPsR30 179.9 14.01 49.7 6.490.51 a Determined by dynamic light scattering (DLS). b DY-547-labelledGL3 siRNA was used to examine the EE %. c Corresponding to the pKa ofthe polymer determined by acid-base titration.

TABLE 6 Size, zeta potential and siRNA encapsulation efficiency (EE %)of the iRGD-NPs of prepared from the mixture of Meo-PEG-b-P(DPA-co-GMA-Rn) and ACUPA-PEG-b-PDPA a No. Size (nm) b Zeta potential (mv) EE %c ACUPA-NPsR6 58.7 6.97 92.1 ACUPA-NPsR8 85.9 7.92 86.9 ACUPA-NPsR1093.6 8.87 76.1 ACUPA-NPsR20 119.4 13.46 58.2 ACUPA-NPsR30 184.1 13.7851.8 a The molar ratio of Meo-PEG-b-P(DPA-co-GMA-Rn) andACUPA-PEG-b-PDPA is 9:1. b Determined by dynamic light scattering (DLS).c DY-547-labelled GL3 siRNA was used to examine the EE %.

The amphiphilic polymer, Meo-PEG-b-P(DPA-co-GMA-R10) (pKa 6.31, FIG.13C) was used to investigate its pH sensitivity. The transmissionelectron microscope (TEM) image of the GL3 siRNA-loaded NPs ofMeo-PEG-b-P(DPA-co-GMA-R10) incubated in PBS buffer at a pH of 6.5indicated that this amphiphilic copolymer was able to assemble withsiRNA to form spherical NPs at a pH of 6.5, with an average size of 90.8nm determined by dynamic light scattering (DLS, FIG. 13A). When thesolution pH decreases to 6.0, there are no observable NPs after 20 minincubation using TEM imaging, indicating a very fast pH sensitivity. Tofurther evaluate the pH sensitivity, a near-infrared dye,Cy5.5-conjugated PEGylated polymer, was mixed withMeo-PEG-b-P(DPA-co-GMA-R10) to prepare the NPs with the aggregation offluorophores inside the hydrophobic cores. Fluorescent images of theCy.5.5 labelled NPs of Meo-PEG-b-P(DPA-co-GMA-R10) at different pHindicated that, with the quenching of the fluorophores, fluorescencesignal is absent at a pH above pKa. However, protonation of the PDPAsegment at pH below pKa causes the NPs to disassemble, leading to adramatic increase in the fluorescence signal. Measuring the fluorescenceintensity upon the pH change reveals that the pH difference from 10 to90% fluorescence activation (ApH10-90%) is 0.39 (FIG. 14) (Wang, Y etal., Nat Mater, 13, (2), 204-212 (2014)). This value is much smallerthan that of small molecule dyes (about 2 pH units) with the same degreeof fluorescence intensity change (Urano, Y et al., Nat Med, 15, (1),104-109 (2009)), demonstrating the ultra-fast pH response rate ofMeo-PEG-b-P(DPA-co-GMA-R10). This characteristic allows the NPs of thispolymer to show a super-fast release of DY547-labelled GL3 siRNA(DY547-siRNA) at a pH below pKa. As shown in FIG. 13D, around 80% of theloaded siRNA has been released within 3 h at a pH of 6.0. Within thesame time frame, less than 30% of the loaded siRNA is released at a pHof 7.4.

Luciferase-expressing HeLa (Luc-HeLa) cells, which are geneticallymodified to stably express both firefly and Renilla luciferase, wereemployed to evaluate the gene silencing efficacy of the siRNA-loadedNPs. The GL3 siRNA was used to selectively suppress firefly luciferaseexpression. Renilla luciferase expression was used as an internal cellviability control. As shown in FIG. 15A, all the siRNA-loaded NPs cansuppress the firefly luciferase expression at a 10 nM siRNA dose, withthe differential silencing efficacy depending on the length of theoligoarginine grafts. However, there is no obvious difference betweenthe NPs with and without the ACUPA ligand. The main reason is theextremely low PSMA expression in HeLa cells (FIGS. 16A-16F), which leadsto a lack of any significant difference in cellular uptake between thesetwo types of NPs (FIGS. 17A-17F). Among these nanoplatforms, the NPsself-assembled from Meo-PEG-b-P(DPA-co-GMA-R8) orMeo-PEG-b-P(DPA-co-GMA-R10) show a better gene silencing efficacy. InParticular, the NPs made with Meo-PEG-b-P(DPA-co-GMA-R10) can reduce thefirefly luciferase expression by about 90%, which is significantly morethan the commercial lipofectamine 2000 (Lipo2K) treatment, which iscapable of around 70% knockdown in luciferase expression. Notably, thereis no obvious cytotoxicity of NPs used for these in vitro transfectionexperiments (FIG. 18). Cytotoxicity of the GL3 siRNA loaded NPs withvarying length of the oligoarginine grafts, R6, R8, R10, R20, and R30;and Lipo2K-GL3 siRNA complex, against Luc-HeLa cells at a 10 nM siRNAdose was compared with free medium. No obvious cytotoxicity of these NPswas observed.

To validate the contention that the optimal silencing efficacy of theNPs prepared from Meo-PEG-b-P(DPA-co-GMA-R10) (NPsR10 and ACUPA-NPsR10)is attributable to their excellent endosomal escape capability,lysotracker green was used to label the endosomes and examined theintracellular distribution of the DY547-siRNA-loaded NPsR10. Theconfocal laser scanning microscope (CLSM) images of Luc-HeLa cellsincubated with the DY547-siRN-loaded NPsR10 for 2 h showed that amajority of the internalized siRNA-loaded NPs enter the cytoplasm after2 h incubation, dramatically demonstrating the excellent endosomalescape ability of the NPs. If the R10 grafts are replaced bytetraethylenepentamine (Meo-PEG-b-P(DPA-co-GMA-TEPA), the endosomalescape ability of the resulting NPs is comparatively weaker, leading toa much lower silencing efficacy (FIGS. 19A-19B). This suggests that the“proton sponge” effect alone is insufficient for endosomal escape (Yu, Het al., ACS Nano, 5, 9246-9255 (2011); Won, Y Y et al., Journal ofControlled Release, 139, (2), 88-93 (2009)). Additionally, the bettersilencing efficacy of NPsR8 and NPsR10 also agrees with the contentionthat the length of oligoarginine for the most efficient membranepenetration is between 8 and 10 arginine residues (Mitchell, D J et al.,The Journal of Peptide Research, 56, (5), 318-325 (2000); Suzuki, T etal., Journal of Biological Chemistry, 277, 2437-2443 (2002); Fuchs, S Met al., Cell. Mol. Life Sci., 63, 1819-1822 (2006))

After screening the nanoplatform with optimal silencing efficacy, itsPCa specificity was evaluated. LNCaP cells, a PCa cell line withover-expressed PSMA (FIG. 16E) (Farokhzad, O C et al., Proceedings ofthe National Academy of Sciences, 103, (16), 6315-6320 (2006)), werechosen for incubation with the NPs. From the flow cytometry profile inFIG. 15B, unlike the Luc-HeLa cells, LNCaP cells showed around 5-foldstronger uptake of the DY547-siRNA-loaded ACUPA-NPsR10 than that ofNPsR10 (FIG. 20). If the cells are pre-treated with the anti-PSMAantibody for 30 min followed by ACUPA-NPsR10 for another 4 h at a 10 nMsiRNA dose, there is no obvious difference in cellular uptake betweenACUPA-NPsR10 and NPsR10, indicating that the high cellular uptake ofACUPA-NPsR10 is built on the specific recognition between the ACUPAligand and the over-expressed PSMA on LNCaP cells. To further validatethis ACUPA-mediated PCa specificity, two other PCa cell lines withextremely low PSMA expression, PC3 and DU145 cells, similar to that ofHeLa cells (FIGS. 16A-16C), were also incubated with theDY547-siRNA-loaded NPs. With the absence of specific interaction betweenthe ACUPA ligand and PSMA, HeLa, PC3, and DU145 cell lines show similarability to internalize the ACUPA-NPsR10 and NPsR10 (FIGS. 17A-17F). Asummary bar graph showing the fluorescence intensity of PSMA inLuc-HeLa, PC3, DU145, 22RV1, and LNCaP cells (FIG. 16F). DU145 cellsexpress moderate amount of PSMA but at less 30% of that of LNCaP cells.

Based on the high PCa specificity of ACUPA-NPsR10, it was furtherexamined whether this siRNA delivery nanoplatform can be used to silencea potential therapeutic target in LNCaP cells. Prohibitin1 (PHB1) is ahighly conserved and multifunctional 32 kDa protein that regulatesvarious cell behaviors such as proliferation, apoptosis, andtranscription (Thuaud, F et al., Chemistry & Biology 20, (3), 316-331;Theiss, A L et al., Biochimica et Biophysica Acta (BBA)—Molecular CellResearch, 1813, (6), 1137-1143 (2011)). Upregulation of PHB1 has beenfound in most cancers including PCa and is associated with drugresistance (Kapoor, S. Human Pathology 44, (4), 678-679; Gregory-Bass, RC et al., International Journal of Cancer, 122, (9), 1923-1930 (2008)).Western blot was employed to investigate the knockdown efficacy of PHB1siRNA-loaded ACUPA-NPsR10. Western blot analysis of PHB1 expression inLNCaP cells treated with PHB1 siRNA-loaded NPsR10 and ACUPA-NPsR10indicated that this siRNA delivery nanoplatform can knock down PHB1 byaround 90% at a 10 nM siRNA dose. Additionally, the PHB1 expression isnearly absent (<2%) at a 50 nM siRNA dose. However, more than 30% of PHBis still expressed in the cells incubated with the siRNA-loaded NPsR10at a 10 nM siRNA dose (FIG. 21). A similar tendency can be also found inthe immunofluorescence staining analysis. Immunofluorescence analysis ofthe LNCaP cells treated by PHB1 siRNA-loaded NPsR10 at a 10 nM siRNAdose showed that red fluorescence corresponding to residual PHB1expression can be observed in the LNCaP cells treated by siRNA-loadedNPsR10 at a 10 nM siRNA dose. In contrast, there is nearly no redfluorescence in the cells treated by siRNA-loaded ACUPA-NPsR10. Withthis suppressed PHB1 expression, LNCaP cells show a very slowproliferation rate (FIG. 15C). After 8 days incubation, there is onlyroughly a 3-fold increase in the cell number at a 10 nM siRNA dose. Incontrast, there is around a 7-fold or 11-fold increase in the number ofcells treated with PHB1 or GL3 siRNA-loaded NPsR10.

After proving the in vitro PCa-specificity of the ACUPA-NPsR10, theirpharmacokinetics and in vivo PCa-specificity was evaluated. Thepharmacokinetics of the ACUPA-NPsR10 was examined by intravenousinjection of DY647 labelled GL3 siRNA (DY647-siRNA) loaded NPs tohealthy mice (650 μg/kg siRNA dose, n=3). As shown in FIG. 22, the bloodhalf-life (t1/2) of ACUPA-NPsR10 is around 4.56 h, far longer than nakedsiRNA (t1/2<30 min). This better stability is mainly attributed toprotection by the PEG outer layer and small particle size (Knop, K etal., Angewandte Chemie International Edition, 49, 6288-6308 (2010); Guo,X et al., Accounts of Chemical Research, 45, 971-979 (2012); Bertrand, Net al., Advanced Drug Delivery Reviews, 66, 2-25(2014). Moreover, due tothe negative nature of the surface-encoded ACUPA ligand with threecarboxylic acid groups, the ACUPA-NPsR10 show a much longer bloodcirculation than NPsR10 (t1/2=4.18 h). The in vivo PCa-specificity ofACUPA-NPsR10 was assessed by intravenously injecting Cy5.5 labelled GL3siRNA (Cy5.5-siRNA) loaded NPs to LNCaP xenograft tumor-bearing mice(650 μg/kg siRNA dose, n=3). Overlaid fluorescent image of the LNCaPxenograft tumor-bearing nude mice 24 h post-injection of nakedCy5.5-siRNA, Cy5.5-siRNA-loaded NPsR10 and ACUPA-NPsR10, and PSMAantibody followed by Cy5.5-siRNA-loaded ACUPA-NPsR10 showed thefluorescent image of the mice at 24 h post-injection. There is almost noaccumulation of naked siRNA in the tumor. However, the ACUPA-NPsR10shows high accumulation in the tumor corresponding to the brightfluorescence. In the absence of the PSMA-specific ACUPA ligand, theaccumulation of NPsR10 in the tumor is much lower compared toACUPA-NPsR10. If first injecting the PSMA antibody (5 mg/kg dose)followed by ACUPA-NPsR10, the blocked PSMA leads to a decrease in theaccumulation of ACUPA-NPsR10 in tumor, highlighting the important effectof specific interaction between PSMA and the ACUPA ligand on thePCa-specificity of ACUPA-NPsR10. To analyze the accumulation of NPs intumor and other organs, the tumor and main organs of mice 24 hpost-injection were harvested and the biodistribution of the NPsdetermined. The naked siRNA presents a characteristic biodistribution,i.e., high accumulation in kidney but extremely low accumulation intumor (Zhu X et al., Proceedings of the National Academy of Sciences,112, (25), 7779-7784 (2015)). With the specific recognition between theACUPA ligand and PSMA over-expressed on LNCaP xenograft tumor, theaccumulation of ACUPA-NPsR10 in tumor is around 3-fold higher than thatof NPsR10 or that found in mice pre-treated with PSMA antibody.

Finally, the in vivo inhibition of PHB1 expression and anti-tumorefficacy was evaluated. To examine the inhibition of PHB1 expression intumor tissue, PHB1 siRNA-loaded NPs were intravenously injected to LNCaPxenograft tumor-bearing mice (650 μg/kg siRNA dose, n=3) on threeconsecutive days and in vivo PHB1 expression was examined by westernblot. Western blot analysis of PHB1 expression in the LNCaP tumor tissueafter systemic treatment by control NPs, PHB1 siRNA-loaded NPsR10 andPHB1 siRNA-loaded ACUPA-NPsR10 indicated that the siRNA loaded NPsinhibited PHB1 expression. With the ACUPA ligand targeting tumortissues, injection of siRNA-loaded ACUPA-NPsR10 leads to more than 70%knockdown of PHB1 expression. In contrast, there is only around 33%knockdown for mice treated with siRNA-loaded NPsR10 (FIG. 24). Inaddition, the administration of NPs shows neglectable in vivo sideeffects. After five consecutive injections of the NPs to healthy mice(once every two days at a 650 μg/kg siRNA dose, n=3), there are nonoticeable histological changes in the tissues from heart, liver,spleen, lung or kidney. To determine whether this NP-mediated PHB1silencing has an anti-tumor effect, the PHB1 siRNA-loaded NPs wereintravenously injected to the LNCaP xenograft tumor-bearing mice (onceevery two days at a 650 μg/kg siRNA dose, n=5). As shown in FIG. 23, thesiRNA loaded NPs do indeed inhibit tumor growth. In particular, due totheir excellent PCa specificity, the siRNA-loaded ACUPA-NPsR10significantly suppress tumor growth after five consecutive injectionsand there is less than a 3-fold increase in the tumor size at 30 daysafter the first injection However, for the mice treated with GL3siRNA-loaded NPsR10 (Control NPs) or PBS, more than 6-fold or 8-foldincrease in the tumor size can be found at 18 days after the firstinjection. Moreover, the administration of the siRNA-loaded ACUPA-NPsR10shows no obvious influence on body weight (FIG. 25), demonstrating thegood biocompatibility of this nanoplatform.

In conclusion, an oligoarginine-functionalized and ultra pH-responsivenanoplatform for PCa-specific siRNA delivery has been developed. Thisnanoplatform can specifically deliver siRNA to PCa through therecognition between the ACUPA ligand and over-expressed PSMA on PCacells. With the endosome swelling induced by ultra pH-responsivecharacteristic along with the oligoarginine-mediated endosomal membranepenetration, this nanoplatform can efficiently escape from endosomes andrapidly release therapeutic siRNA in the cytoplasm, leading to asignificant inhibition of cancer-associated PHB1 expression and tumorgrowth. The targeted membrane-penetrating and ultra pH-responsivenanoplatform is effective as a robust siRNA delivery vehicle forPCa-specific therapy.

Example 3: Ultra pH-Responsive Nanoparticles (NPs) as Nanoprobe forCancer Diagnostics Methods and Materials Synthesis of Meo-PEG-Br andBr-PEG-COOH

The detailed synthesis is same as the description in Examples 1 and 2.

Synthesis of methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate) (Meo-PEG-b-P(DPA-co-GMA))

Meo-PEG113-b-P(DPA80-co-GMA5) copolymer was synthesized according to thesame method described in Example 1.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA)

Meo-PEG-b-P(DPA-co-GMA-TEPA) was synthesized according to the samemethod described in Example 1.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5)

Meo-PEG-b-P(DPA-co-GMA-TEPA) (0.2 g) and Cy5.5 NHS ester (1.5-fold molarexcess relative to the TEPA repeating unit) were well dissolved in 5 mLof THF. After constantly stirring in dark for 48 h, the solution wasdialyzed against deionized water and the product was collected afterfreeze-drying. The synthesis scheme is shown above.

Synthesis of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)

Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) was synthesized according to the samemethod described in Example 1.

Preparation of Cy5.5-labelled NPs

The THF solution of Meo-PEG-b-P(DPA-co-GMA-TEPA-C14) (4 mg/mL) andMeo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5) (4 mg/mL) was mixed in a volume ratioof 8:2. Under vigorously stirring (1000 rpm), 0.5 mL of the mixture wasadded dropwise to 5 mL of deionized water. After collection andpurification by an ultrafiltration device (EMD Millipore, MWCO 100 kDa),the NPs formed were dispersed in 1 mL of PBS buffers (pH 7.4). The sizeand zeta potential of the Cy5.5-labelled NPs were determined by DLS. Themorphology of NPs was visualized on TEM. Before observation, the samplewas stained with 1% uranyl acetate and dried under air.

Evaluation of pH Responsiveness

The Cy5.5-labelled NPs were prepared as described above and thendispersed in 1 mL of deionized water. Subsequently, 1 M NaOH or HCl wasadded in 1-5 μL increments, and the fluorescence intensity of the NPswas measured on a Synergy HT multi-mode microplate reader. Thenormalized fluorescence intensity (NFI) vs. pH profile was used toquantitatively assess the pH responsiveness. NFI is calculated asfollows:

NFI=(F−F _(min))/(F _(max) −Fmin)

where F is the fluorescence intensity of the NPs at any given pH valueand F_(max) and F_(min) are the maximal and minimal fluorescenceintensity of the NPs, respectively.

Results

Imaging agents such as fluorescent dye can also be conjugated to theultra pH-responsive copolymer to prepare dye-labelled NPs for diseasediagnostics. The fluorescent dye can be, but is not limited to, Cy5.5.Cy5.5 was conjugated to the structure of the ultra pH-responsivecopolymer (FIG. 26A). This dye-labelled copolymer can self-assemble intoNPs with the aggregation of fluorophores inside the hydrophobic cores(FIG. 26B). Due to the quenching of the fluorophores, fluorescencesignal is absent at a pH above pKa. However, protonation of the PDPAsegment at pH below pKa causes the NPs to disassemble, leading to adramatic increase in the fluorescence signal. Measuring the fluorescenceintensity upon the pH change reveals that the pH difference from 10 to90% fluorescence activation (ApH10-90%) is 0.39 (FIG. 2A). This value ismuch smaller than that of small molecule dyes (about 2 pH units) withthe same degree of fluorescence intensity change, demonstrating theultra-fast pH response characteristic of the NPs. Compared to normaltissue, the microenvironment of tumor tissue is weakly acidic.Therefore, the dye-labelled ultra pH-responsive NPs can be applied fortargeted cancer diagnostics.

Example 4: Ultra pH-Responsive Nanoplatform for Anticancer Drug Deliveryand Cancer Therapy Methods and Materials Synthesis of Meo-PEG-Br andBr-PEG-COOH

The detailed synthesis is same as the description in Examples 1 and 2.

Synthesis of methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate) (Meo-PEG-b-PDPA)

Meo-PEG113-b-PDPA80 copolymer was synthesized by using ATRP method. Inbrief, DPA-MA (2.6 g, 12 mmol), Meo-PEG-Br (0.75 g, 0.15 mmol), andPMDETA (31.5 4, 0.15 mmol) were added to a polymerization tube. DMF (3mL) and 2-propanol (3 mL) were then added to dissolve the monomer andinitiator. After three cycles of freeze-pump-thaw to remove oxygen, CuBr(21.6 mg, 0.15 mmol) was added under nitrogen atmosphere and thepolymerization tube was sealed under vacuum. After polymerization at 40°C. for 24 h, tetrahydrofuran (THF) was added to dilute the product,which was then passed through a neutral Al₂O₃ column to remove thecatalyst. The resulting THF solution was concentrated and the residuewas dialyzed against THF, followed by deionized water. The expectedcopolymer was collected as a white powder after freeze-drying undervacuum.

Acid-Base Titration

Meo-PEG-b-PDPA was dispersed in deionized water, and a concentrated HClaqueous solution was added until the copolymer was completely dissolved(1 mg/mL). Subsequently, 1 M NaOH aqueous solution was added in 1-5 μLincrements. After each addition, the solution was constantly stirred for3 min, and the solution pH was measured using a pH meter. The pKa of thecopolymer was determined as the pH at which 50% of the copolymer turnsionizes.

Preparation and Characterization of Nanoparticles (NPs)

Meo-PEG-b-PDPA was dissolved in THF to form a homogenous solution with aconcentration of 5 mg/mL. Subsequently, a certain volume of this THFsolution was taken and added dropwise to 4 mL of deionized water undervigorously stirring (1000 rpm). The NP dispersion formed was transferredto an ultrafiltration device (EMD Millipore, MWCO 100 K) and centifugedto remove the organic solvent and free compounds. After washing with PBS(pH 7.4) solution (3×5 mL), the NPs were dispersed in 1 mL of phosphatebuffered saline (PBS, pH 7.4) solution. Size and zeta potential weredetermined by DLS. The morphology of NPs was visualized on TEM. Beforeobservation, the sample was stained with 1% uranyl acetate and driedunder air.

To prepare the PTX loaded NPs, a certain volume of polymer solution (5mg/mL in THF) was taken and mixed with PTX (20 μL, 20 mg/mL THFsolution). Under vigorously stirring (1000 rpm), the mixture was addeddropwise to 4 mL of deionized water. The NPs were collected and purifiedaccording to the same method describe above. To determine the PTXencapsulation efficiency, a small volume (50 μL) of the NP solution waswithdrawn and mixed with 20-fold DMSO. The UV absorption was examined ona UV-Vis spectrometer and compared to the free PTX solution (5 μL stocksolution mixed with 20-fold DMSO).

In Vitro Drug Release

The PTX loaded NPs were prepared as described above. Subsequently, theNPs were dispersed in 1 mL of PBS (pH 7.4) and then transferred to aFloat-a-lyzer G2 dialysis device (MWCO 100 kDa, Spectrum) that wasimmersed in PBS (pH 7.4) at 37° C. At a predetermined interval, 5 μL ofthe NP solution was withdrawn and mixed with 20-fold DMSO. The UVabsorption was examined on a UV-Vis spectrometer and compared to thestandard PTX work curve. The average value of three independentexperiments was collected and the cumulative PTX release was calculatedas follows:

Cumulative PTX release (%)=(M _(t) /M _(∞))×100

where M_(t) is the amount of PTX released from the micelles and is theamount of PTX loaded in the micelles.

In Vitro Cytotoxicity

Prostate cancer cells (PC3, DU145 and LNCaP) were seeded in a 96-wellplate with a density of 5000 cells/well. After the incubation in 100 μLof RPMI-1640 containing 10% FBS for 24 h, a fixed amount of PTX loadedNPs dispersed in 100 μL of RPMI-1640 was added and the cells wereallowed to incubate for another 48 h. After replacing the medium with100 pt of fresh RPMI-1640, 10 μL of alamarBlue agent was added to eachwell and the cells were further incubated for 1 h. The cytotoxicity wasmeasured using the alamarBlue assay according to the manufacturer'sprotocol. The average value of six independent experiments was collectedand the cell viability was calculated as follows:

Viability (%)=(OD _(treated) /OD _(control))×100

where OD_(control) is obtained in the absence of the PTX loaded NPs andOD_(treated) is obtained in the presence of the PTX loaded NPs.

Results

Chemotherapeutic drugs can be also encapsulated into the ultrapH-responsive NPs for disease treatment. The chemotherapeutic drugs canbe, but are not limited to, docetaxel (DTX), paclitaxel (PTX),doxorubicin (DOX), mitoxantrone (MTX), etc. Ultra pH-responsivePEGylated copolymer was synthesized (FIG. 27A), which can co-assemblewith anticancer drug PTX to form spherical NPs with PTX loaded in theirhydrophobic core as observed in TEM images taken of the NPs ofMeo-PEG-b-PDPA in PBS buffer at a pH of 7.4. The PTX loading efficacy ismore than 10% and the size of the PTX loaded NPs is around 100 nm. TEMimages of the NPs of Meo-PEG-b-PDPA in PBS buffer at a pH of 5.0 showedthat with the rapid protonation of the ultra pH-responsive copolymer,there are no observable NPs at a pH below pKa, thus leading to asuper-fast PTX release (FIG. 27B).

Example 5: Light-Responsive Nanoplatform for Anticancer Drug Deliveryand Cancer Therapy Methods and Materials Synthesis of2-(2-oxo-2-phenylacetoxy) ethyl methacrylate (OPEMA)

Phenylglyoxylic acid (PGA, 13.5 g, 90 mmol), 2-hydroxyethyl methacrylate(HEMA, 21.06 g, 162 mmol), and 4-dimethylaminopyridine (DMAP) were welldissolved 200 mL of DCM. In an ice-salt bath,N,N′-dicyclohexylcarbodiimide (DCC, 22.2 g, 108 mmol) dissolved in 110mL of DCM was added. After reaction at room temperature overnight, themixture was filtered and filtration was washed with water (3×50 mL), 10%HCl (3×50 mL), and saturated Na2CO3 solution (3×50 mL). After dryingover anhydrous Na2SO4, the solvent was removed and the final product wascollected as powder. The synthesis scheme is shown below.

Synthesis of Meo-PEG-Br and Br-PEG-COOH

The detailed synthesis is same as the description in Examples 1 and 2.

Synthesis of methoxyl-polyethylene glycol-b-poly(2-(2-oxo-2-phenylacetoxy) ethyl methacrylate) (Meo-PEG-b-POPEMA)

Meo-PEG113-b-POPEMA80 copolymer was synthesized using ATRP method. Inbrief, OPEMA (3.15 g, 12 mmol), Meo-PEG-Br (0.75 g, 0.15 mmol), andPMDETA (31.5 μL, 0.15 mmol) were added to a polymerization tube. DMF (3mL) and 2-propanol (3 mL) were then added to dissolve the monomer andinitiator. After three cycles of freeze-pump-thaw to remove oxygen, CuBr(21.6 mg, 0.15 mmol) was added under nitrogen atmosphere and thepolymerization tube was sealed under vacuum. After polymerization at 40°C. for 24 h, tetrahydrofuran (THF) was added to dilute the product,which was then passed through a neutral Al₂O₃ column to remove thecatalyst. The resulting THF solution was concentrated and the residuewas dialyzed against THF, followed by deionized water. The expectedcopolymer was collected as a white powder after freeze-drying undervacuum.

The synthesis scheme is shown below.

Preparation and Characterization of Nanoparticles (NPs)

Meo-PEG-b-POPEMA was dissolved in THF to form a homogenous solution witha concentration of 10 mg/mL. Subsequently, a certain volume of this THFsolution was taken and added dropwise to 5 mL of deionized water undervigorously stirring (1000 rpm). The NP dispersion formed was transferredto an ultrafiltration device (EMD Millipore, MWCO 100 K) and centrifugedto remove the organic solvent and free compounds. After washing with PBS(pH 7.4) solution (3×5 mL), the NPs were dispersed in 1 mL of phosphatebuffered saline (PBS, pH 7.4) solution. Size and zeta potential weredetermined by DLS. The morphology of NPs was visualized on TEM. Beforeobservation, the sample was stained with 1% uranyl acetate and driedunder air.

Determination of Light-Sensitivity

The NPs of Meo-PEG-b-POPEMA were prepared as described above and thendispersed in 1 mL of deionized water. The solution of the NPs was placedunder 365 nm UV light (16 W) for different time periods. The size of theNPs was examined at pre-determined time points. After 24 h UVirradiation, the solution was freeze-dried and the sample was dissolvedin DMF for GPC analysis.

Preparation of Drug Loaded NPs

To prepare the drug loaded NPs, a certain volume of the polymer solution(10 mg/mL in THF) was taken and mixed with PTX (20 μL, 20 mg/mL THFsolution). Under vigorously stirring (1000 rpm), the mixture was addeddropwise to 4 mL of deionized water. The NPs were collected and purifiedaccording to the same method describe above. To determine the PTXencapsulation efficiency, a small volume (50 μL) of the NP solution waswithdrawn and mixed with 20-fold DMSO. The UV absorption was examined ona UV-Vis spectrometer and compared to the free PTX solution (5 μL stocksolution mixed with 20-fold DMSO).

In Vitro Drug Release

The PTX loaded NPs were prepared as described above. Subsequently, theNPs were dispersed in 1 mL of PBS (pH 7.4) and then transferred to aFloat-a-lyzer G2 dialysis device (MWCO 100 kDa, Spectrum) that wasimmersed in PBS (pH 7.4) at 37° C. At a predetermined interval, 5 μL ofthe NP solution was withdrawn and mixed with 20-fold DMSO. The UVabsorption was examined on a UV-Vis spectrometer and compared to thestandard PTX work curve. The average value of three independentexperiments was collected and the cumulative PTX release was calculatedas follows:

Cumulative PTX release (%)=(M _(t) /M _(∞))×100

where M_(t) is the amount of PTX released from the micelles and is theamount of PTX loaded in the micelles.

In Vitro Cytotoxicity

Prostate cancer cells (PC3, DU145 and LNCaP) were seeded in a 96-wellplate with a density of 5000 cells/well. After the incubation in 100 μLof RPMI-1640 containing 10% FBS for 24 h, a fixed amount of PTX loadedNPs dispersed in 100 μL of RPMI-1640 was added and the cells wereallowed to incubate for another 48 h. After replacing the medium with100 μL of fresh RPMI-1640, 10 μL of alamarBlue agent was added to eachwell and the cells were further incubated for 1 h. The cytotoxicity wasmeasured using the alamarBlue assay according to the manufacturer'sprotocol. The average value of six independent experiments was collectedand the cell viability was calculated as follows:

Viability (%)=(OD _(treated) /OD _(control))×100

where OD_(control) is obtained in the absence of the PTX loaded NPs andOD_(treated) is obtained in the presence of the PTX loaded NPs.

Results

Stimuli-responsive amphiphilic copolymers can be used to prepare the NPsfor delivery of therapeutic and diagnostic agents including but notlimited to genes, chemotherapeutic drugs, or other small molecules.These amphiphilic polymers can be, but not limited to, light-, redox-,and temperature-responsive polymers. The light-sensitive monomer,2-(2-oxo-2-phenylacetoxy) ethyl methacrylate (OPEMA) was synthesized,and atom-transfer radical polymerization (ATRP) was used to synthesizethe PEGylated light-sensitive copolymer: (FIG. 28A). Under 365 nm UVlight irradiation, this copolymer can be degraded and there issignificant decrease in its molecular weight (FIG. 28B). Due to theamphiphilic nature, this copolymer can self-assemble into spherical NPswith an average size of 80 nm as seen in TEM images of the NPs ofMeo-PEG-b-POPEMA in PBS buffer (pH 7.4) before 365 nm UV lightirradiation. Under 365 nm UV light irradiation for 30 min, there are noobserved NPs under transmission electron microscope observed in the TEMimages of the NPs of Meo-PEG-b-POPEMA in PBS buffer (pH 7.4). Thismorphological change leads to a rapid release of loaded anticancer drugDTX (FIG. 29A) and efficient anticancer activity (FIG. 29B).

Example 6: Fast Redox-Responsive Nanoplatform for siRNA Delivery withRobust Anti-Cancer Efficacy Methods and Materials Synthesis of theL-cystine-based poly(disulfide) (PDSA) polymers

PDSA polymers were prepared by one-step polycondensation of L-cystinedimethyl ester dihydrochloride ((H-Cys-OMe)2.2HCl) and dichlorides orBis-nitrophenol esters of different fatty diacids. A standard synthesisprocedure was carried out as follows: (H-Cys-OMe)2.2HCl (10.0 mmol) andtriethylamine (15 mmol) were dissolved in 20.0 mL DMSO, then thedichloride of fatty acid (10.0 mmol) DMSO solution (10.0 mL) was addedinto the cystine mixture solution dropwise. The solution was stirred for15 mins to obtain a uniform mixture, precipitated twice in 250 mL ofcold ethyl ether, and dried under reduced atmosphere. The final productwas a yellow or brown yellow powder. The synthesis scheme is shownbelow.

Redox-Responsive Behavior of the PDSA Polymers

GPC analysis was used to study the redox-responsive behavior of the PDSApolymers. The polymer (1 mg) was dissolved in 2 mL of DMF/H2O (9:1, V/V)and then GSH (6.2 mg, 0.02 mmol) was added to obtain a solution with GSHconcentration of 10 mM. At predetermined intervals, 100 μL of thesolution was taken for GPC analysis.

Preparation and Characterization of Nanoparticles (NPs)

The PDSA polymers were dissolved in DMF or DMSO to form a homogenoussolution with a concentration of 20 mg/mL. Subsequently, 200 μL of thissolution was taken and mixed with 140 μL of DSPE-PEG3000 (20 mg/mL inDMF), 50 μL of G0-C14 (5 mg/mL in DMF) and 1 nmol siRNA (0.1 nmol/μLaqueous solution). Under vigorously stirring (1000 rpm), the mixture wasadded dropwise to 5 mL of deionized water. The NP dispersion formed wastransferred to an ultrafiltration device (EMD Millipore, MWCO 100 K) andcentrifuged to remove the organic solvent and free compounds. Afterwashing with PBS (pH 7.4) solution (3×5 mL), the siRNA loaded NPs weredispersed in 1 mL of phosphate buffered saline (PBS, pH 7.4) solution.Size and zeta potential were determined by DLS. The morphology of NPswas visualized on TEM. To determine the siRNA encapsulation efficiency,DY547-labelled GL3 siRNA (DY547-siRNA) loaded NPs were preparedaccording to the method described above. A small volume (50 μL) of theNP solution was withdrawn and mixed with 20-fold DMSO. The fluorescenceintensity of DY547-siRNA was measured using a Synergy HT multi-modemicroplate reader (BioTek Instruments) and compared to the free DY-547labelled GL3 siRNA solution (1 nmol/mL PBS solution).

Redox-Responsive Behavior of the NPs

The siRNA loaded NPs were prepared as described above and dispersed inPBS containing 10 mM GSH. At pre-determined time point, the particlesize was examined by DLS and the particle morphology was observed onTEM. To evaluate the intracellular redox-responsive behavior, the NPswith Nile red and coumarin 6 encapsulated in their hydrophobic coreswere prepared and then incubated with HeLa cells for different time. Thefluorescence of Nile red and coumarin 6 was observed a FV1000 confocallaser scanning microscope (CLSM, Olympus). If the NPs respond to redoxstimulus, the Nile red and coumarin 6 will release and only greenfluorescence of coumarin 6 can be observed under CLSM. If the NPs areintact, the fluorescence of coumarin 6 will be quenched by Nile red andonly red fluorescence can be observed under CLSM.

Evaluation of Endosomal Escape

Luc-HeLa cells (20,000 cells) were seeded in discs and incubated in 1 mLof RPMI 1640 medium containing 10% FBS for 24 h. Subsequently, theDY547-siRNA-loaded NPs were added, and the cells were allowed toincubate for 1 or 2 h. After removing the medium and subsequentlywashing with PBS (pH 7.4) solution thrice, the endosomes and nuclei werestained with lysotracker green and Hoechst 33342, respectively. Thecells were then viewed under CLSM.

In Vitro siRNA Release

DY547-siRNA-loaded NPs were prepared as described above.

Subsequently, the NPs were dispersed in 1 mL of PBS (pH 7.4) and thentransferred to a Float-a-lyzer G2 dialysis device (MWCO 100 kDa,Spectrum) that was immersed in PBS (pH 7.4) at 37° C. At a predeterminedinterval, 5 μL of the NP solution was withdrawn and mixed with 20-foldDMSO. The fluorescence intensity of DY547-siRNA was determined bySynergy HT multi-mode microplate reader.

Luciferase Silencing

Luc-HeLa cells were seeded in 96-well plates (5,000 cells per well) andincubated in 0.1 mL of RPMI 1640 medium with 10% FBS for 24 h.Thereafter, the GL3 siRNA-loaded NPs were added. After incubating for 24h, the cells were washed with fresh medium and allowed to incubate foranother 48 h. The expression of firefly luciferase in HeLa cells wasdetermined using Steady-Glo luciferase assay kits. Cytotoxicity wasmeasured using the alamarBlue assay according to the manufacturer'sprotocol. The luminescence or fluorescence intensity was measured usinga microplate reader, and the average value of five independentexperiments was collected. As a control, the silencing effect ofLipo2K/GL3 siRNA complexes was also evaluated according to the proceduredescribed above and compared to that of GL3 siRNA-loaded NPs.

In Vitro KIF11 Silencing

Prostate cancer cells (PC3, LNCaP, DU145 and 22Rv1) were seeded in6-well plates (50,000 cells per well) and incubated in 1 mL of RPMI 1640medium containing 10% FBS for 24 h. Subsequently, the cells weretransfected with the KIF11 siRNA-loaded NPs for 24 h. After washing thecells with PBS thrice, the cells were further incubated in fresh mediumfor another 48 h. Thereafter, the cells were digested by trypsin and theproteins were extracted using modified radioimmunoprecipitation assaylysis buffer (50 mM Tris-HCl pH 7.4, 150 mM NaCl, 1% NP-40 substitute,0.25% sodium deoxycholate, 1 mM sodium fluoride, 1 mM Na3VO4, 1 mMEDTA), supplemented with protease inhibitor cocktail and 1 mMphenylmethanesulfonyl fluoride (PMSF). The expression of KIF11 wasexamined using the western blot analysis.

In Vitro Cell Proliferation

PC3 cells were seeded in 6-well plates (20,000 cells per well) andincubated in 1 mL of RPMI 1640 medium containing 10% FBS for 24 h.Thereafter, the cells were transfected with the KIF11 siRNA-loaded NPsfor 24 h and then washed with fresh medium for further incubation. Atpredetermined intervals, the cytotoxicity was measured using thealamarBlue assay according to the manufacturer's protocol. After eachmeasurement, the alamarBlue agent was removed and the cells wereincubated in fresh medium for further proliferation.

PC3 Xenograft Tumor Model

The tumor model was constructed by subcutaneous injection with 200 μL ofLNCaP cell suspension (a mixture of RPMI 1640 medium and Matrigel in 1:1volume ratio) with a density of 2×10⁶ cells/mL into the back region ofhealthy male BALB/c nude mice. When the volume of the PC3 tumorxenograft reached ˜50 mm³, the mice were used for the following in vivoexperiments.

Pharmacokinetics Study

Healthy male BALB/c mice were randomly divided into two groups (n=3) andgiven an intravenous injection of either (i) free DY647-labelled GL3siRNA (DY647-siRNA) and (ii) DY647-siRNA-loaded NPs at a 650 μg/kg siRNAdose. At predetermined time intervals, orbital vein blood (20 μL) waswithdrawn using a tube containing heparin, and the wound was pressed forseveral seconds to stop the bleeding. The fluorescence intensity ofDY-647 labelled siRNA in the blood was determined using a microplatereader. The blood circulation half-life (t1/2) was calculated byfirst-order decay fit.

Biodistribution

PC3 tumor-bearing male BALB/c nude mice were randomly divided into twogroups (n=3) and given an intravenous injection of either (i) freeDY677-labelled GL3 siRNA (DY677-siRNA) or (ii) DY677-siRNA-loaded NPs ata 650 μg/kg siRNA dose. Twenty-four hours after the injection, the micewere imaged using the Maestro 2 In-Vivo Imaging System (Cri Inc). Mainorgans and tumors were then harvested and imaged. To quantify theaccumulation of NPs in tumors and organs, the fluorescence intensity ofeach tissue was quantified by Image-J.

In Vivo KIF11 Silencing

PC3 tumor-bearing male BALB/c nude mice were randomly divided into twogroups (n=3) and intravenously injected with (i) KIF11 siRNA-loaded NPsor (ii) GL3 siRNA-loaded NPs at a 650 μg/kg siRNA dose for threeconsecutive days. Twenty-four hours post the final injection, mice weresacrificed and tumors were harvested. The proteins in the tumor wereextracted using modified radioimmunoprecipitation assay lysis buffer (50mM Tris-HCl pH 7.4, 150 mM NaCl, 1% NP-40 substitute, 0.25% sodiumdeoxycholate, 1 mM sodium fluoride, 1 mM Na₃VO₄, 1 mM EDTA),supplemented with protease inhibitor cocktail and 1 mMphenylmethanesulfonyl fluoride (PMSF). The expression of KIF11 wasexamined using the aforementioned western blot analysis.

Inhibition of Tumor Growth

PC3 tumor-bearing male BALB/c nude mice were randomly divided into fourgroups (n=5) and intravenously injected with (i) PBS, (ii) Naked KIF11siRNA, (iii) Blank NPs, and (iv) KIF11 siRNA-loaded NPs at a 650 μg/kgsiRNA dose. All the mice were administrated four injections and thetumor growth was monitored every two days by measuring perpendiculardiameters using a caliper and tumor volume was calculated as follows:

V=W ² ×L/2

where W and L are the shortest and longest diameters, respectively.

Histology

Healthy male BALB/c mice were randomly divided into three groups (n=3)and administered daily intravenous injections of either (i) PBS or (ii)KIF11 siRNA-loaded NPs at a 650 μg/kg siRNA dose. After four consecutiveinjections (once every two days), the main organs were collected 2 dayspost the final injection, fixed with 4% paraformaldehyde, and embeddedin paraffin. Tissue sections were stained with hematoxylin-eosin (H&E)and viewed under an optical microscope.

Results

Besides amphiphilic copolymers, hydrophobic polymers can be also used todevelop stimuli-responsive NPs for various biomedical applications. Forthese hydrophobic polymers, their NPs are prepared by using the mixtureof the hydrophobic polymer and amphiphilic compound. The amphiphiliccompound can be, but is not limited to, one or a plurality of thefollowing: naturally derived lipids, lipid-like materials, surfactants,synthesized amphiphilic compounds, or combinations thereof.

Redox-responsive hydrophilic polymer was synthesized which couldco-assemble with lipid-PEG to form spherical NPs for gene delivery andcancer therapy (FIG. 30). The intracellular levels of glutathione (GSH)are 100-1000 fold higher in cancer cells than in normal tissue.Redox-sensitive approach is particularly promising to enhance theexposure of cancer cells to therapeutic molecules. In this example,L-cystine dimethyl ester and fatty diacid were used to synthesize alibrary of L-cystine-based poly(disulfide amide) polymers (PDSA).

Feed compositions and molecular weight of the PDSA polymers aresummarized in Table 7. Taking PDSA8-1, for example, with the presence ofmany disulfide bonds, there is a significant decrease in the moleculeweight of PDSA8-1 incubated in 10 mM glutathione (GSH) solution. Whenmixing this redox-responsive polymer with DSPE-PEG3000, siRNA andcationic lipid (Xiaoyang Xu et al. Proc Natl Acad Sci USA, 110,18638-18643(2013)) in water miscible solvent such as DMF, DMSO, THF,etc., spherical NPs with an average size of ˜100 nm (as seen in TEMimage of the NPs of the PDSA8-1) can be formed via nanoprecipitationmethod, in which hydrophilic PEG chains are on the outer shell and siRNAis encapsulated in the hydrophobic core. The physiochemical propertiesof other PDSA polymers are summarized in Table 8. With theredox-responsive characteristic to induce the breakage of the NPs ofPDSA8-1 (FIG. 31A and observed by TEM imaging), the siRNA loaded NPs ofPDSA8-1 show efficient endosomal escape ability as seen in fluorescentimages of HeLa cells incubated with the siRNA loaded NPs of tPDSA8-1 for1 hour and 4 hour time points; and high efficacy in down-regulation ofluciferase expression in HeLa cells (>90% knockdown at 1 nM siRNA dose,FIG. 31B). These redox-responsive NPs can be used as a robustnanoplatform to deliver therapeutic siRNA for prostate cancer therapy.After treatment with the NPs loading kinesin family member 11 (KIF11)siRNA, there is a significant decrease in the expression of KIF11 infour prostate cancer cell lines (PC3, LNCaP, 22Rv1 and DU145) at a verylow siRNA dose by Western blot analysis of KIF11 expression in prostatecancer cells treated with KIF11 siRNA loaded NPs of PDSA8-1. Especiallyfor PC3 cells, there is nearly no KIF11 expression at an extremely lowsiRNA dose (5 nM) as seen by immunofluorescence analysis of PC3 cellstreated by KIF11 siRNA loaded NPs of PDSA8-1 at a 0 and 5 nM siRNA dose.With this down-regulated KIF11 expression, the proliferation rate of PC3cells is significantly inhibited and there is around 80% decrease in thecell number decreases at a siRNA dose of 10 nM (FIG. 32). In vivoexperiment results demonstrated that these NPs have a long bloodcirculation (FIG. 33) and show high accumulation in PC3 xenograft tumorof mice as seen in overlaid fluorescent image of the PC3 xenografttumor-bearing nude mice 24 h post systemic injection of nakedDY677-siRNA, and DY677-siRNA loaded NPs of PDSA8-1. This lead to around90% knockdown of KIF11 expression in tumor tissue assessed by Westernblot analysis of KIF11 expression in the PC3 tumor tissue after systemictreatment by KIF11 siRNA loaded NPs of PDSA8-1 (FIG. 34), andsignificant inhibition of tumor growth within 52 days (FIG. 35).

TABLE 7 Feed compositions and molecular weight of the PDSA polymers.Poly(disulfide amide) M_(n) ^(a) M_(w) ^(a) Polydispersity ^(a) m = 4PDSA4 2900 4300 1.48 m = 6 PDSA6 3900 5700 1.48 m = 8 PDSA8-1 5700 73001.43 m = 10 PDSA10 9100 13200 1.45 m = 8 PDSA8-2 4700 7800 1.66 m = 8PDSA8-3 9300 15200 1.63 m = 8 PDSA8-4 11700 16600 1.42 ^(a)Determined byGPC using DMF as the client.

TABLE 8 Size, siRNA encapsulation efficiency (EE %) and zeta potentialof the NPs of PDSA polymers. PDSA4 PDSA6 PDSA8-1 PDSA10 PDSA8-2 PDSA8-3PDSA8-4 Size (nm) ^(a) 155.7 134.5 102.9 87.6 118.9 99.4 93.4 EE % ^(b)29.7 35.1 55.9 82.9 46.3 79.4 88.2 ξ (mV) −6.79 −8.08 −11.21 −15.05−9.79 −12.05 −20.01 ^(a) N:P ratio is 20:1; ^(b) siRNA encapsulationefficiency.

Example 7: Ultra pH-Responsive Nanoplatform for Anticancer Drug Deliveryand Cancer Therapy Methods and Materials Synthesis of poly(2-(diisopropylamino) ethylmethacrylate (PDPA)

DPA was synthesized by radical polymerization using 2-aminoethanethiolhydrochloride (AET.HCl) as a chain transfer agent. In brief, DPA-MA(4.27 g, 20 mmol), AET.HCl (0.88 mmol, 0.1 g), and AIBN (18 mg, 0.11mmol) were dissolved in 15 mL of DMF. The solution was degassed bybubbling with nitrogen for 30 min. The mixture reacted at 70° C. for 6 hunder nitrogen. Then, the product was precipitated by the addition ofchilled methanol. The final PDPA was collected after drying in vacuumfor 24 h.

Preparation and Characterization of Nanoparticles (NPs)

The PDPA polymer was dissolved in THF to form a homogenous solution witha concentration of 5 mg/mL. Subsequently, 250 μL of this solution wastaken and mixed with 125 μL of DSPE-PEG3000 solution (5 mg/mL in DMF).Under vigorously stirring (1000 rpm), the mixture was added dropwise to5 mL of deionized water. The NP dispersion formed was transferred to anultrafiltration device (EMD Millipore, MWCO 100 K) and centrifuged toremove the organic solvent and free compounds. After washing with PBS(pH 7.4) solution (3×5 mL), the final NPs were dispersed in 1 mL ofphosphate buffered saline (PBS, pH 7.4) solution. Size and zetapotential were determined by DLS. The morphology of NPs was visualizedon TEM.

Ultra pH-Responsive Behavior of the NPs

The pH-responsive behavior of the NPs was evaluated by examining theparticle size change at a pH below pKa. In brief, the NPs of PDPA wereprepared as described above and then dispersed in deionized water. Afteradding concentrated HCl solution to adjust the solution pH to a value of5.0, the particle size was examined by DLS.

Preparation of PTX Loaded Nanoparticles (NPs)

To prepare the paclitaxel (PTX) loaded NPs, a certain volume of polymersolution (5 mg/mL in THF) was taken and mixed with 125 μL ofDSPE-PEG3000 solution (5 mg/mL in DMF) and PTX (20 μL, 20 mg/mL THFsolution). Under vigorously stirring (1000 rpm), the mixture was addeddropwise to 5 mL of deionized water. The NPs were collected and purifiedaccording to the same method describe above. To determine the PTXencapsulation efficiency, a small volume (50 μL) of the NP solution waswithdrawn and mixed with 20-fold DMSO. The UV absorption was examined ona UV-Vis spectrometer and compared to the free PTX solution (54 stocksolution mixed with 20-fold DMSO).

In Vitro Drug Release

The PTX loaded NPs were prepared as described above. Subsequently, theNPs were dispersed in 1 mL of PBS (pH 7.4) and then transferred to aFloat-a-lyzer G2 dialysis device (MWCO 100 kDa, Spectrum) that wasimmersed in PBS (pH 7.4) at 37° C. At a predetermined interval, 54 ofthe NP solution was withdrawn and mixed with 20-fold DMSO. The UVabsorption was examined on a UV-Vis spectrometer and compared to thestandard PTX work curve. The average value of three independentexperiments was collected and the cumulative PTX release was calculatedas follows:

Cumulative PTX release (%)=(Mt/M∞)×100

where Mt is the amount of PTX released from the micelles and Moo is theamount of PTX loaded in the micelles.

In Vitro Cytotoxicity

Prostate cancer cells (PC3, DU145 and LNCaP) were seeded in a 96-wellplate with a density of 5000 cells/well. After the incubation in 100 μLof RPMI-1640 containing 10% FBS for 24 h, a fixed amount of PTX loadedNPs dispersed in 100 μL of RPMI-1640 was added and the cells wereallowed to incubate for another 48 h. After replacing the medium with100 μL of fresh RPMI-1640, 10 μL of alamarBlue agent was added to eachwell and the cells were further incubated for 1 h. The cytotoxicity wasmeasured using the alamarBlue assay according to the manufacturer'sprotocol. The average value of six independent experiments was collectedand the cell viability was calculated as follows:

Viability (%)=(ODtreated/ODcontrol)×100

where ODcontrol is obtained in the absence of the PTX loaded NPs andODtreated is obtained in the presence of the PTX loaded NPs

Results

Other than the previously discussed redox-responsive polymer, otherhydrophobic polymers can be also used to mix with one or moreamphiphilic polymers to prepare stimuli-responsive NPs for delivery oftherapeutic and diagnostic agents including genes, chemotherapeuticdrugs, or other small molecules. These hydrophobic polymers can be, butnot limited to pH-, light-, and temperature-responsive polymers. UltrapH-responsive polymer, poly(2-(diisopropylamino) ethylmethacrylate)(PDPA) was synthesized.

This polymer is hydrophobic at a pH above pKa but becomes hydrophilic ata pH below pKa. Mixing this polymer with DSPE-PEG3000 and anticancerdrug PTX in water miscible solvent, spherical NPs with an average sizeof 90 nm can be formed with PTX encapsulated into their hydrophobic coreas seen by TEM imaging of the NPs of PDPA in PBS buffer at a pH of 7.4.Due to the ultra pH-responsive characteristic, these NPs show asuper-fast PTX release at a pH below pKa seen by TEM imaging of the NPsof PDPA in PBS buffer at a pH of 5.0 (FIG. 22).

Example 8: Tumor Microenvironment (TME) pH-Responsive MultistagedNanoparticle Platform for siRNA Delivery and Cancer Therapy Methods andMaterials

Materials 2-(Hexamethyleneimino) ethanol, methacryloyl chloride, andhydroquinone were purchased from Alfa Aesar Company and used directly.α-Bromoisobutyryl bromide, N,N′-dimethylformamide (DMF), triethylamine(TEA), N,N,N′,N′,N′-pentamethyldiethylenetriamine (PMDETA), copper (I)bromide (CuBr), isopropyl alcohol, dichloromethane (DCM),tetrahydrofuran (THF), and diethyl ether were provided by Sigma-Aldrichand used as received. Methoxyl-polyethylene glycol (Meo-PEG₁₁₃-OH) waspurchased from JenKem Technology. Tumor-targeting and cell-penetratingpeptide-amphiphiles (TCPA1: C₁₇H₃₅CONH-GR₈GRGDS-OH; TCPA2:C₁₇H₃₅CONH—(C₁₇H₃₅CONH)—KR₈GRGDS-OH) were obtained from GL Biochem Ltd.2-Aminoethyl methacrylate (AMA) were purchased from Polyscience Company.Cyanine5.5 NHS ester was purchased from Lumiprobe. Lipofectamine 2000(Lipo2K) was purchased from Invitrogen. Steady-Glo luciferase assaysystem was provided by Promega. Fluorescent dye DY677-labelled Luc andBRD4 siRNAs were acquired from GE Dharmacon. The siRNA sequences are asfollows: Luc siRNA, 5′-CUU ACG CUG AGU ACU UCG AdTdT-3′ (sense) (SEQ IDNO:1) and 5′-UCG AAG UAC UCA GCG UAA GdTdT-3′ (antisense) (SEQ ID NO:2);BRD4 siRNA, 5′-AAA CAC AAC UCA AGC AUC GUU-3′ (sense) (SEQ ID NO:9) and5′-CGA UGC UUG AGU UGU GUU UUU-3′ (antisense) (SEQ ID NO:10). DY677 waslabelled at the 5′-end of both the sense and antisense strands of LucsiRNA. Fluorescein and its quencher (Dabcyl)-labelled Luc siRNA was alsoprovided by GE Dharmacon. Fluorescein was labelled at the 5′-end of thesense strand and Dabcyl was labelled at 3′-end of the antisense strand.HeLa cells stably expressing firefly luciferase (Luc-HeLa) were obtainedfrom Alnylam Pharmaceuticals, Inc. The cells were incubated in RPMI 1640medium (Invitrogen) with 10% fetal bovine serum (FBS, Sigma-Aldrich).All other reagents and solvents are of analytical grade and used withoutfurther purification.

Synthesis of 2-(hexamethyleneimino) ethyl methacrylate (HMEMA)

2-(Hexamethyleneimino) ethanol (0.1 mol, 14.3 g), TEA (0.12 mol, 12.1g), and inhibitor hydroquinone (0.001 mol, 0.11 g) were dissolved in 100mL of THF and then methacryloyl chloride (0.1 mol, 10.5 g) was addeddropwise. After refluxing for 2 h, the precipitation was removed and theTHF solvent was removed by rotary evaporator. The resulting residue wasdistilled under vacuum as a colorless liquid. The synthesis of HMEMA isshown below.

Synthesis Scheme of HMEMA

Synthesis of Meo-PEG-Br

Meo-PEG-Br was synthesized according to the same method described inExample 1.

Synthesis of methoxyl-polyethylene glycol-b-poly(2-(hexamethyleneimino)ethyl methacrylate) (Meo-PEG-b-PHMEMA)

Meo-PEG-b-PHMEMA block copolymer was synthesized by atom transferradical polymerization (ATRP). HMEMA (12 mmol), Meo-PEG-Br (0.15 mmol),and PMDETA (0.15 mmol) were added to a polymerization tube. DMF (3 mL)and 2-propanol (3 mL) were then added to dissolve the monomer andinitiator. After three cycles of freeze-pump-thaw to remove oxygen, CuBr(0.15 mmol) was added under nitrogen atmosphere and the polymerizationtube was sealed under vacuum. After polymerization at 40° C. for 24 h,tetrahydrofuran (THF) was added to dilute the product, which was thenpassed through a neutral Al₂O₃ column to remove the catalyst. Theresulting THF solution was concentrated and the residue was dialyzedagainst THF, followed by deionized water. The expected polymer wascollected as a white powder after freeze-drying under vacuum. Thesynthesis of Meo-PEG-b-PHMEMA is shown below. The molecular weight wasdetermined by gel permeation chromatography (GPC) using THF as eluent.M_(n,GPC)=2.34×10⁴ (PDI=1.25); M_(n,NMR)=2.15×10⁴.

Synthesis Scheme of Meo-PEG-b-PHMEMA

Synthesis of methoxyl-polyethylene glycol-b-poly (2-(hexamethyleneimino)ethyl methacrylate-co-2-aminoethyl methacrylate)(Meo-PEG-b-P(HMEMA-co-AMA))

Meo-PEG-b-P(HMEMA-co-AMA) copolymer was synthesized by ATRP. HMEMA (6mmol), Meo-PEG-Br (0.075 mmol), and PMDETA (0.075 mmol) were added to apolymerization tube. DMF (1.5 mL) and 2-propanol (1.5 mL) were thenadded to dissolve the monomer and initiator. After three cycles offreeze-pump-thaw to remove oxygen, CuBr (0.075 mmol) was added undernitrogen atmosphere and the polymerization tube was sealed under vacuum.After polymerization at 40° C. for 24 h, tetrahydrofuran (THF) was addedto dilute the product, which was then passed through a neutral Al₂O₃column to remove the catalyst. The resulting THF solution wasconcentrated and the residue was dialyzed against THF, followed bydeionized water. The expected polymer was collected as a white powderafter freeze-drying under vacuum. The synthesis ofMeo-PEG-b-P(HMEMA-co-AMA) is shown below. The molecular weight wasdetermined by gel permeation chromatography (GPC) using THF as eluent.M_(n,GPC)=2.42×10⁴ (PDI=1.33); M_(n,NMR)=2.23×10⁴.

Synthesis of Meo-PEG-b-P(HMEMA-co-AMA-Cy5.5)

Meo-PEG-b-P(HMEMA-co-AMA) (0.5 g) and Cy5.5 NHS ester (1.5-fold molarexcess relative to the AMA repeating unit) were well dissolved in 15 mLof DMF. After constantly stirring in dark for 48 h, the solution wasdialyzed against DMF for 48 h followed deionized water for 72 h. Theproduct was collected after freeze-drying. The synthesis ofMeo-PEG-b-P(HMEMA-co-AMA-Cy5.5) is shown below.

Synthesis Scheme of Meo-PEG-b-P(HMEMA-co-AMA) andMeo-PEG-b-P(HMEMA-co-AMA-Cy5.5)

Gel Permeation Chromatography (GPC)

Number- and weight-average molecular weights (M_(n) and M_(w),respectively) of the polymers were determined by a gel permeationchromatographic system according to the same method described in Example1.

¹H Nuclear Magnetic Resonance (¹HNMR)

The ¹HNMR spectra of the polymers were recorded according to the samemethod described in Example 1.

Acid-Base Titration

Meo-PEG-b-PHMEMA was dispersed in deionized water, and a concentratedHCl aqueous solution was added until the copolymer was completelydissolved (1 mg/mL). Subsequently, 1 M NaOH aqueous solution was addedin 1-5 μL increments. After each addition, the solution was constantlystirred for 3 min, and the solution pH was measured using a pH meter.The pKa of the copolymer was determined as the pH at which 50% of thecopolymer turns ionized.

Evaluation of pH Sensitivity

A DMF solution of Meo-PEG-b-PHMEMA (5 mg/mL) andMeo-PEG-b-P(HMEMA-co-AMA-Cy5.5) (5 mg/mL) was mixed in a volume ratio of1:1. Under vigorously stirring (1000 rpm200 μL of the mixture was addeddropwise to 5 mL of deionized water. After collection and purificationusing ultrafiltration device (EMD Millipore, MWCO 100 kDa), the NPsformed were dispersed in 1 mL of phosphate buffered saline (PBS, pH7.4). Subsequently, 1 M NaOH or HCl aqueous solution was added in 1-5 μLincrements, and fluorescence intensity with an excitation of 675 nm wasmeasured on a Synergy HT multi-mode microplate reader (BioTekInstruments). The normalized fluorescence intensity (NFI) vs. pH profilewas used to quantitatively assess the pH responsiveness. NFI iscalculated as follows:

NFI=(F−F _(min))/(F _(max) −F _(min))

where F is the fluorescence intensity of the NPs at any given pH valueand Fmax and Fmin are the maximal and minimal fluorescence intensity ofthe NPs, respectively.

Preparation of the siRNA Loaded Nanoparticles (NPs)

Meo-PEG-b-PHMEMA was dissolved in DMF to form a homogenous solution witha concentration of 10 mg/mL. Subsequently, a mixture of 1 nmol siRNA(0.1 nmol/4 aqueous solution) and TCPA (5 mg/mL in DMF) in an N/P molarratio of 1:20 was prepared and mixed with 200 μL of Meo-PEG-b-PHMEMAsolution. Under vigorously stirring (1000 rpm), the mixture was addeddropwise to 5 mL of deionized water. The NP dispersion formed wastransferred to an ultrafiltration device (EMD Millipore, MWCO 100 K) andcentrifuged to remove the organic solvent and free compounds. Afterwashing with PBS buffer (pH 7.4) (3×5 mL), the siRNA loaded NPs weredispersed in 1 mL of PBS buffer (pH 7.4).

Characterizations of NPs

Size and zeta potential were determined by dynamic light scattering(DLS, Brookhaven Instruments Corporation). The morphology of NPs wasvisualized on a Tecnai G2 Spirit BioTWIN transmission electronmicroscope (TEM). Before observation, the sample was stained with 1%uranyl acetate and dried under air. To determine siRNA encapsulationefficiency (EE %), DY677-labelled Luc siRNA (DY677-siRNA) loaded NPswere prepared according to the method aforementioned. A small volume (5μL) of the NP solution was withdrawn and mixed with 20-fold DMSO. Thestandard was prepared by mixing 54 of naked DY677-siRNA solution (1nmol/mL in pH 7.4 PBS buffer) with 20-fold DMSO. The fluorescenceintensity of DY677-siRNA was measured using a microplate reader and thesiRNA EE % is calculated as: EE %=(FI_(NPs)/FI_(Standard))×100.

Digestion Assay

NPs loaded with fluorescein- and Dabcyl-labelled Luc siRNA were preparedaccording to the method aforementioned, and then dispersed in 1 mL ofPBS buffer. Subsequently, 20 U RNase was added and the sample wasincubated in 37° C. At predetermined time intervals, the fluorescentemission spectra were examined using a microplate reader with excitationat 480 nm and emission data range between 490 and 650 nm.

In Vitro siRNA Release

DY677-labelled Luc siRNA loaded NPs were prepared as described above.Subsequently, the NPs were dispersed in 1 mL of PBS (pH 7.4) and thentransferred to a Float-a-lyzer G2 dialysis device (MWCO 100 kDa,Spectrum) that was immersed in PBS buffer (pH 7.4 or 6.8) at 37° C. At apredetermined interval, 5 μL of the NP solution was withdrawn and mixedwith 20-fold DMSO. The fluorescence intensity of DY677-labelled siRNAwas determined using a microplate reader.

Flow Cytometry

Luc-HeLa (50,000 cells) were seeded in 6-well plate and incubated in 2mL of RPMI1640 medium (pH 7.4) containing 10% FBS for 24 h. Afterreplacing the medium with 2 mL of fresh medium at pH 7.4 or 6.8,DY677-labelled Luc siRNA loaded NPs were added, and the cells wereallowed to incubate for 2 h. After removing the medium and subsequentlywashing with PBS buffer (pH 7.4) thrice, the cells were digested bytrypsin and collected for flow cytometry quantitative analysis (DXP11Analyzer).

Confocal Laser Scanning Microscope (CLSM)

Luc-HeLa (50,000 cells) were seeded in round discs and incubated in 2 mLof RPMI1640 medium (pH7.4) containing 10% FBS for 24 h. After replacingthe medium with 2 mL of fresh medium at pH 7.4 or 6.8, DY677-labelledLuc siRNA loaded NPs were added, and the cells were allowed to incubatefor 2 h. After removing the medium and subsequently washing with PBSbuffer (pH 7.4) thrice, lysotracker green was added to stain theendosomes and the nuclei were stained by Hoechst 33342. The uptake ofsiRNA loaded NPs were viewed under a FV1000 CLSM (Olympus).

Luc Silencing

Luc-HeLa cells were seeded in 96-well plates (5,000 cells per well) andincubated in 0.1 mL of RPMI1640 medium (pH 7.4) with 10% FBS for 24 h.Thereafter, the medium was replaced by fresh medium at Luc siRNA-loadedNPs were added. After 24 h incubation, the cells were washed with PBSbuffer (pH 7.4) and allowed to incubate in fresh medium (pH 7.4) foranother 48 h. The Luc expression in HeLa cells was determined usingSteady-Glo luciferase assay kits. Cytotoxicity was measured usingAlamarBlue assay according to the manufacturer's protocol. Theluminescence or fluorescence intensity was measured using a microplatereader, and the average value of five independent experiments wascollected.

In Vitro BRD4 Silencing

LNCaP cells were seeded in 6-well plates (50,000 cells per well) andincubated in 2 mL of RPMI1640 medium (pH 7.4) containing 10% FBS for 24h. Subsequently, the medium was replaced by fresh medium at pH 7.4 or6.8, and then BRD4 siRNA loaded NPs were added. After incubation for 24h, the cells were washed with PBS buffer (pH 7.4) and further incubatedin fresh medium (pH 7.4) for another 48 h. Thereafter, the cells weredigested by trypsin and the proteins were extracted using modifiedradioimmunoprecipitation assay lysis buffer (50 mM Tris-HCl pH 7.4, 150mM NaCl, 1% NP-40 substitute, 0.25% sodium deoxycholate, 1 mM sodiumfluoride, 1 mM Na3VO4, 1 mM EDTA), supplemented with protease inhibitorcocktail and 1 mM phenylmethanesulfonyl fluoride (PMSF). The BRD4expression was examined using the western blot analysis.

Western Blot Analysis

Western blot analysis was carried according to the same method describedin Example 1. BRD4 rabbit antibody (Abcam) and beta-actin rabbitantibody (Cell Signaling) were used. The BRD4 expression was detectedwith horseradish peroxidase (HRP)-conjugated secondary antibody(anti-rabbit IgG HRP-linked antibody, Cell Signaling) and an enhancedchemiluminescence (ECL) detection system (Pierce).

Apoptosis Analysis

LNCaP cells were seeded in 6-well plates (50,000 cells per well) andincubated in 2 mL of RPMI1640 medium (pH 7.4) containing 10% FBS for 24h. Subsequently, the medium was replaced by fresh medium at pH 7.4 or6.8, and then BRD4 siRNA loaded NPs were added. After incubation for 24h, the cells were washed with PBS buffer (pH 7.4) and further incubatedin fresh medium (pH 7.4) for another 48 h. Thereafter, the cells weredigested by trypsin and the cells were collected for 7-amino-actinomycin(7-AAD) and PE Annexin V staining using PE Annexin V Apoptosis DetectionKit I (BD Pharmingen™). The apoptosis analysis was performed using aDXP11 Flow Cytometry Analyzer.

Immunofluorescence Staining

LNCaP cells (50,000 cells) were seeded in round disc and incubated in 2mL of RPMI1640 medium (pH 7.4) containing 10% FBS for 24 h. Afterreplacing the medium with fresh medium (pH 7.4 or 6.8), BRD4 siRNAloaded NPs were added and the cells were allowed to incubated for 24 h.Subsequently, the cells were washed with PBS buffer (pH 7.4) and freshmedium (pH 7.4) was added. After 48 h incubation, the cells were fixedwith 4% paraformaldehyde. The cells were then permeabilized byincubation in 0.2% Triton X-100 in PBS buffer (pH 7.4) for 5 minutes,followed by washing with pH 7.4 PBS buffer (3×5 min). Thereafter, thecells were blocked with blocking buffer (2% normal goat serum, 2% BSA,and 0.2% gelatin in pH 7.4 PBS buffer) at room temperature for 1 h.After washing the cells with pH 7.4 PBS buffer (3×5 min), BRD4 rabbitantibody (Abcam) diluted in 1% BSA solution was added and the cells wereincubated for 1 h. Subsequently, the cells were with pH 7.4 PBS buffer(3×5 min), and then further incubated with Alex Fluro 647-linkedsecondary antibody and Alex Fluro 488-conjugated phalloidin for another1 h. After washing with pH 7.4 PBS buffer (3×5 min), the cells wereviewed under a FV1000 CLSM.

In Vitro Cell Proliferation

LNCaP cells were seeded in 6-well plates (20,000 cells per well) andincubated in 2 mL of RPMI1640 medium (pH 7.4) containing 10% FBS for 24h. Thereafter, the cells were treated with the BRD4 siRNA loaded NPs atpH 7.4 or 6.8 for 24 h and then washed with PBS buffer (pH 7.4) forfurther incubation. At predetermined intervals, the cytotoxicity wasmeasured by AlamarBlue assay according to the manufacturer's protocol.After each measurement, the AlamarBlue agent was removed and 2 mL offresh medium (pH 7.4) was added for further incubation.

Pharmacokinetics Study

Healthy male BALB/c mice were randomly divided into two groups (n=3) andgiven an intravenous injection of either (i) DY677-labelled naked LucsiRNA or (ii) DY677-labelled Luc siRNA loaded NPs at a 1 nmol siRNA doseper mouse. At predetermined time intervals, orbital vein blood (20 μL)was withdrawn using a tube containing heparin, and the wound was pressedfor several seconds to stop the bleeding. The fluorescence intensity ofDY677-labelled siRNA in the blood was determined by microplate reader.The blood circulation half-life (t_(1/2)) was calculated according toprevious report (Winter H et al., Antimicrob. Agents Chemother. 57,5516-5520 (2013)).

LNCaP Xenograft Tumor Model

LNCaP xenograft tumor model was constructed by subcutaneous injectionwith 200 μL of LNCaP cell suspension (a mixture of RPMI 1640 medium andMatrigel in 1:1 volume ratio) with a density 1×10⁷ cells/mL into theback region of healthy male Athymic nude mice. When the volume of theLNCaP tumor xenograft reached ˜70 mm³, the mice were used for thefollowing in vivo experiments.

Biodistribution

LNCaP tumor-bearing male Athymic nude mice were randomly divided intothree groups (n=3) and given an intravenous injection of either (i)DY677-labelled naked Luc siRNA or (ii) DY677-labelled Luc siRNA loadedNPs at a 1 nmol siRNA dose per mouse. Twenty-four hours after theinjection, the mice were imaged using the Maestro 2 In-Vivo ImagingSystem (Cri Inc). Organs and tumors were then harvested and imaged. Toquantify the accumulation of NPs in tumors and organs, the fluorescenceintensity of each tissue was quantified by Image-J.

In Vivo BRD4 Silencing

LNCaP tumor-bearing male Athymic nude mice were randomly divided intotwo groups (n=2) and intravenously injected with (i) Luc siRNA loadedNPs or (ii) BRD4 siRNA loaded NPs for three consecutive days.Twenty-four hours after the final injection, mice were sacrificed andtumors were harvested for western blot analysis, andimmunohistochemistry and TUNEL staining. For the western blot analysis,the proteins in the tumor were extracted using modifiedradioimmunoprecipitation assay lysis buffer (50 mM Tris-HCl pH 7.4, 150mM NaCl, 1% NP-40 substitute, 0.25% sodium deoxycholate, 1 mM sodiumfluoride, 1 mM Na₃VO₄, 1 mM EDTA), supplemented with protease inhibitorcocktail and 1 mM phenylmethanesulfonyl fluoride (PMSF). Western blotwas performed according to the method described above.

Immunohistochemistry (IHC) Staining

IHC staining was performed on formalin-fixed paraffin-embedded tumorsections. Briefly, tumor slides were first heated to 60° C. for 1 h,desparaffinized with xylene (3×5 min), and washed with differentconcentrations of alcohol. After retrieval of antigen using DAKO targetretrieval solution at 95-99° C. for 40 min, followed by washing, theslides were blocked with peroxidase blocking buffer (DAKO Company) for 5min. After washing buffer (DAKO Company), the slides were incubated withBRD4 rabbit antibody (Abcam) diluted in DAKO antibody solution for 1 h.The slides were then washed and incubated with peroxidase-labeledpolymer for 30 min. After washing and staining with DAB+substrate-chromogen solution and hematoxylin, the slides we remountedand viewed under a MVX10 MacroView Dissecting scope equipped withOlympusDP80 camera.

Immune Response

Healthy male BALB/c mice were randomly divided into three groups (n=3)and given an intravenous injection of either (i) PBS, (ii) naked BRD4siRNA or (iii) BRD4 siRNA loaded NPs at a 1 nmol siRNA dose per mouse.Twenty-four hours after injection, blood was collected and serumisolated for measurements of representative cytokines (TNF-α, IL-6,IL-12, and IFN-γ) by enzyme-linked immunosorbent assay or ELISA (PBLBiomedical Laboratories and BD Biosciences) according to themanufacturer's instructions.

Histology

Healthy male BALB/c mice were randomly divided into three groups (n=3)and administered daily intravenous injections of either (i) PBS, (ii)naked BRD4 siRNA or (iii) BRD4 siRNA loaded NPs at a 1 nmol siRNA doseper mouse. After three consecutive injections, the main organs werecollected 24 h post the final injection, fixed with 4% paraformaldehyde,and embedded in paraffin. Tissue sections were stained withhematoxylin-eosin (H&E) and then viewed under an optical microscope.

Inhibition of Tumor Growth

LNCaP tumor-bearing male Athymic nude mice were randomly divided intofour groups (n=4) and intravenously injected with (i) PBS, (ii) nakedBRD4 siRNA, (iii) Luc siRNA loaded NPs, or (iv) BRD4 siRNA loaded NPs ata 1 nmol siRNA dose per mouse once every three days. All the mice wereadministrated by administered four consecutive injections and the tumorgrowth was monitored every two days by measuring perpendicular diametersusing a caliper and tumor volume was calculated as follows:

V=W ² ×L/2

where W and L are the shortest and longest diameters, respectively.

Statistical Analysis

Statistical significance was determined by a two-tailed Student's t testassuming equal variance. A p value <0.05 is considered statisticallysignificant.

Results

Most of current delivery systems can overcome one or a few barriers, butunfortunately encounter various dilemmas (e.g., long circulation vs.weak uptake and active targeting vs. unfavorable circulation) to inducesuboptimal therapeutic effect. RNAi technology has demonstrated thepotential to make a huge impact on cancer treatment by silencing theexpression of target gene(s), especially those that encode “undruggable”proteins (Kay, M A, Nat Rev Genet 2011, 12, (5), 316-328; Yin H et al.,Nat Rev Genet 2014, 15, (8), 541-555; Grimm, D. Advanced Drug DeliveryReviews 2009, 61, (9), 672-703; Zhu X et al., Proceedings of theNational Academy of Sciences 2015, 112, (25), 7779-7784; Xu X et al.,Angewandte Chemie International Edition 2016, 55, (25), 7091-7094).24-29Nevertheless, systemic delivery of RNAi agents (e.g., siRNA) to solidtumor followed by sufficient cytosolic siRNA release has remained abarrier to the clinical translation of RNAi therapy (Pack D W et al.,Nat Rev Drug Discov 2005, 4, (7), 581-593; Whitehead K A et al., Nat RevDrug Discov 2009, 8, (2), 129-138; Tseng Y C et al., Advanced DrugDelivery Reviews 2009, 61, (9), 721-731; Pan D W et al., BioconjugateChemistry 2015, 26, (8), 1791-1803). Currently, the de-PEGylationtechnique is a commonly used strategy to promote siRNA deliveryefficacy, in which PEG chains can be cleaved by the acidic pH34 orover-expressed metalloprotease (MMP) in tumor tissues to simultaneouslyachieve high tumor accumulation and enhanced cellular uptake (HatakeyamaH et al., Biomaterials 2011, 32, (18), 4306-4316; Wang H X et al.,Biomaterials 2014, 35, (26), 7622-7634;). However, the complicated TMEstimuli-responsive chemistry involved in this strategy may introduceadditional complexities in the synthesis and scale-up of therapeuticformulations.

Here, a tumor microenvironment (TME) pH-responsive multistaged NPplatform for systemic siRNA delivery and effective cancer therapy hasbeen developed. This NP platform is composed of a polyethylene glycol(PEG) outer shell and a super-fast TME pH-responsive core that canentrap the complex formed between siRNA and a tumor cell-targeting and-penetrating peptide-amphiphile (TCPA). After encapsulating siRNA, theresulting NP platform shows the following features for multistaged siRNAdelivery (FIG. 37): i) polyethylene glycol (PEG) outer shell prolongsblood circulation and thus enhances tumor accumulation; ii) super-fastTME pH response of the hydrophobic poly(2-(hexamethyleneimino) ethylmethacrylate) (PHMEMA) induces the rapid exposure of siRNA/TCPAcomplexes at tumor site; iii) tumor cell-targeting ability of TCPAimproves the uptake of the exposed siRNA/TCPA complexes by tumor cells;iv) cell-penetrating ability of TCPA enhances the cytosolic siRNAdelivery to achieve efficient gene silencing; and v) ease of polymersynthesis and commercial available TCPA facilitate the scale-up of thismultistaged NP platform using standard unit operations.

First, classic acid-base titration was used to examine the pKa of theTME pH-responsive polymer, methoxyl-polyethyleneglycol-b-poly(2-(hexamethyleneimino) ethyl methacrylate)(Meo-PEG-b-PHMEMA), and the pKa value is determined as ˜6.9, which isclose to the pH of tumor extracellular fluid (6.5˜6.8) (Wang Y et al.,Nat Mater 2014, 13, (2), 204-212.). This result suggests that a TMEpH-responsive cargo release can be achieved when using a carrierformulated with the Meo-PEG-b-PHMEMA polymer. To further support this, anear-infrared dye, Cy5.5, was incorporated into the hydrophobic PHMEMAmoiety (Meo-PEG-b-P(HMEMA-AMA-Cy5.5)). When mixing this Cy5.5-labelledpolymer with Meo-PEG-b-PHMEMA (1:1 in molar ratio), they canself-assemble into well-dispersed NPs visualized by transmissionelectron microscopy (TEM), with an average size of ˜40 nm determined bydynamic light scattering (DLS). Due to the quenching of the aggregatedfluorophores inside the hydrophobic cores of these NPs, there is nofluorescence signal at a pH above pKa of Meo-PEG-b-PHMEMA (FIG. 38A). Incontrast, at a pH below pKa, the protonated PHMEMA moiety leads to thedisassembly of the NPs, visualized by TEM, and a dramatic increase inthe fluorescence signal (FIG. 38A). Measurement of the fluorescenceintensity upon pH change shows that the pH difference from 10 to 90%fluorescence activation (ΔpH10-90%) is 0.24 (FIG. 38B), which is closeto the previous report and much smaller than that of small molecule dyes(about 2 pH units), demonstrating the super-fast TME pH response of theMeo-PEG-b-PHMEMA polymer (Zhou K et al., Angewandte Chemie InternationalEdition 2011, 50, (27), 6109-6114; Urano Y et al., Nat Med 2009, 15,(1), 104-109).

The siRNA loading ability and TME pH-responsive behavior of the siRNAloaded NPs was investigated. Nanoprecipitation method was employed toprepare the NPs by using a mixture of siRNA aqueous solution anddimethylformamide (DMF) solution of Meo-PEG-b-PHMEMA and TCPA. Two TCPAs(TCPA1: C17H35CONH-GR8GRGDS-OH; TCPA2:C17H35CONH—(C17H35CONH)-KR8GRGDS-OH, chemical structures shown below)were used to adjust the siRNA loading ability and physiochemicalproperties of the NPs (denoted TCPA1-NPs and TCPA2-NPs). Under the sameconditions, the siRNA encapsulation efficiency (EE %, Table 9) of theTCPA1-NPs (˜39%) is lower than that of TCPA2-NPs (˜52%). In contrast,the size of the TCPA1-NPs (˜90.1 nm, with PDI 0.279) is larger than thatof the TCPA2-NPs (˜72.8 nm, with PDI 0.194), determined by DLS. Thepossible reason is that the two hydrophobic tails of TCPA2 facilitatethe formation of more compact TCPA2/siRNA complexes to improve the siRNAloading ability and decrease the size of the NPs (Lim Y B et al.,Angewandte Chemie International Edition 2007, 46, (47), 9011-9014). Inaddition, the TCPA2-NPs show a strong ability to protect the siRNAstability. When encapsulating fluorescein and its quencher(Dabcyl)-labelled siRNA into the NPs, there is nearly no fluorescencechange after 6 h incubation with RNase (FIG. 39). However, naked siRNAcan be rapidly degraded by RNase at 5 min, 10 min, and 15 min, whichinduces the dissociation between fluorescein and Dabcyl, and therebysignificant increase of the fluorescence intensity.

TABLE 9 Size, zeta potential, and siRNA encapsulation efficiency (EE %)of the siRNA loaded NPs made with of Meo-PEG-b-PHMEMA and TCPA1 orTCPA2. Zeta potential (mv) NPs siRNA EE (%) Size (nm) pH 7.4 pH 6.8TCPA1-NPs 39 90.1 9.27 29.2 TCPA2-NPs 52 72.8 5.69 27.6

The TCPA2-NPs were chosen to evaluate their TME pH-responsive behavior.The DY-677 siRNA loaded TCPA2-NPs showed a spherical morphology at pH7.4 under TEM. After adjusting the solution pH to 6.8, there is asignificant decrease in the NP number within 1 min (FIG. 40A),indicating the super-fast TME pH response of the siRNA loaded NPs.Transmission electron microscopy (TEM) measurements show that there aresome large amorphous aggregates and small size particles in thesolution, which possibly correspond to the ionized polymer and exposedTCPA2/siRNA complexes. This result is further confirmed by DLS analysis,in which particles ranging from several nanometers to thousandnanometers can be detected (FIG. 40B). With this rapid disassembly uponpH change, the TCPA2-NPs offer a fast release of DY677-labelled siRNA(DY677-siRNA) (FIG. 40C). More than 80% of loaded siRNA has beenreleased within 4 hours at pH 6.8. Within the same time frame, less than20% of the loaded siRNA is released at pH 7.4.

Molecular Structures of TCPA1 and TCPA2

Next, the ability of this TME pH-triggered NP disassembly to improvecellular uptake of loaded siRNA and to enhance gene silencing wasinvestigated. Luciferase-expressing HeLa (Luc-HeLa) cells were incubatedwith the DY677-siRNA loaded TCPA2-NPs at pH 6.8 or 7.4 for 2 h, and thecellular uptake was observed by confocal laser scanning microscopy(CLSM). Endosomes were stained by lysotracker green; nuclei were stainedby Hoechst 33342. Compared to the cells incubated at pH 7.4, thebrighter red fluorescence indicates a higher siRNA uptake at pH 6.8.More importantly, unlike the cells incubated at pH 7.4 with theinternalized siRNA co-localizing with lysosomes and endosomes, lots ofthe internalized siRNA molecules at pH 6.8 are distributed in thecytoplasm where siRNA functions. Flow cytometry was used toquantitatively examine the uptake at different pHs. As shown in FIGS.41A-41B, the siRNA uptake at pH 6.8 is more than 5-fold stronger thanthat of the cells incubated at pH 7.4. All these results stronglydemonstrate that the TME pH-triggered disassembly of the TCPA2-NPsinduces the rapid exposure of the TCPA2/siRNA complexes, whichsubsequently use their tumor cell-targeting and -penetrating functionsto dramatically increase the cytosolic siRNA delivery (Sun C Y et al.,Journal of the American Chemical Society 2015, 137, (48), 15217-15224;Xu X D et al., Polymer Chemistry 2012, 3, (9), 2479-2486; Ren Y et al.,Science translational medicine 2012, 4, (147), 147ra1 12; Xu X et al.,ACS Nano 2017).

Next, Luc siRNA was encapsulated into the TCPA2-NPs and their genesilencing efficacy was evaluated using Luc-HeLa cells. As shown in FIG.41C, the siRNA loaded NPs show a reduction in Luc expression at both pH7.4 and 6.8. In comparison, due to rapid disassembly of the NPs at pH6.8 to increase the cytosolic siRNA delivery (FIGS. 41A-41C), they offermuch better gene silencing efficacy and can silence ˜90% Luc expressionwithout obvious cytotoxicity at a 10 nM siRNA dose (FIG. 41D). Theability of the TCPA2-NPs to silence the expression of BRD4 was examined.BRD4 is a conserved member of the BET family of chromatin readers thatexhibits anti-proliferation effect in metastatic castration-resistantprostate cancer (mCRPC). LNCaP cells, an Androgen Receptor (AR) positivePCa cell line with high level of BRD4 expression compared to other PCacells including PC3, 22RV1, and DU145. Thus, LNCaP cells were used as amodel cell line. As shown in FIG. 42A, the BRD4 siRNA loaded NPs showeda higher efficacy in BRD4 silencing at pH 6.8, determined by Westernblot. Around 60% BRD4 can be knocked down at a 10 nM siRNA dose and thisBRD4 silencing reaches ˜90% at a 20 nM siRNA dose. In comparison, forthe cells treated with the BRD4 siRNA loaded NPs at pH 7.4, there isstill a high level of BRD4 expression (>60%) at a 20 nM siRNA dose.Similar results can be also found in the immunofluorescence staininganalysis. At a 20 nM siRNA dose, bright red fluorescence correspondingto the residual BRD4 was observed in the cells treated with the siRNAloaded NPs at pH 7.4. However, very weak red fluorescence is observablein the cells treated with the siRNA loaded NPs at pH 6.8. With thisefficient BRD4 silencing at pH 6.8, the percentage of apoptotic(Annexin-V positive) or necrotic (Annexin V-negative and 7-ADD-postivie)cells increases markedly to 39.5% or 36.3% (FIG. 42B), which is around2.5-flod higher than that of the cells treated with the siRNA loaded NPsat pH 7.4. In addition, the BRD4 silencing also induces significantinhibition of cell proliferation. Only 20% of the LNCaP cells are aliveafter 6 days incubation (FIG. 42C). However, there is about 8-foldincrease in the number of cells treated with the siRNA loaded NPs at pH7.4.

The pharmacokinetics and biodistribution of the TCPA2-NPs was subsequentassessed. Pharmacokinetics was examined by intravenous injection ofDY677-siRNA loaded NPs to health mice (1 nmol siRNA dose per mouse,n=3). As shown in FIG. 43A, with the protection of PEG outer layer,(Knop K et al., Angewandte Chemie International Edition 2010, 49, (36),6288-6308) the TCPA2-NPs show long blood circulation with a half-life(t₁₁₂) of around 4.38 h. In contrast, the naked siRNA is rapidly clearedfrom the blood and its blood half-life (t_(1/2)) is less than 10 min.The biodistribution was evaluated by intravenously injecting DY677-siRNAloaded NPs into LNCaP xenograft tumor-bearing mice. Due to the longblood circulation characteristic of the TCPA2-NPs, they show a muchhigher tumor accumulation than naked siRNA when visualized using thefluorescent image of the LNCaP xenograft tumor-bearing nude mice 24hours post injection of naked DY677-siRNA and siRNA loaded TCPA2-NPs.The tumors and main organs were harvested 24 h post injection and thebiodistribution is shown in FIG. 43B. Naked siRNA has a highaccumulation in kidney but very low accumulation in tumor. However, theTCPA-NPs show an approximately 10-fold higher tumor accumulation thanthe naked siRNA.

The results of above in vitro and in vivo experiments demonstrate thatthe TCPA2-NPs have a high tumor accumulation via long blood circulation,and can respond to TME pH to target and penetrate tumor cells to induceefficient gene silencing, which is a typical multi-staged deliverycharacteristic (Wang S. et al., ACS Nano 2016, 10, (3), 2991-2994; WangS. et al., Advanced materials 2016, 28, (34), 7340-64; Chen B et al.,Theranostics 2017, 7, (3), 538-558).

As a proof of concept, bromodomain 4 (BRD4) was chosen as a therapeutictarget and systematically evaluated the BRD4 siRNA delivery and itsanticancer efficacy. BRD4 is a conserved member of the bromodomain andextraterminal (BET) family of chromatin readers, which plays a criticalrole in tran-scription by RNA polymerase II (RNA Pol II) by facilitatingrecruitment of the positive transcription elongation factor b (P-TEFb)(Jang, M K et al., Molecular Cell 2005, 19, (4), 523-534; Yang, Z etal., Molecular Cell 2005, 19, (4), 535-545.). For mCRPC, BRD4 physicallyinteracts with the N-terminal domain of androgen receptor (AR), a keyfactor that predominantly drives primary prostate cancer (PCa) to mCRPCafter androgen-deprivation therapy (Taylor B S et al., Cancer Cell 2010,18, (1), 11-22; Chen C D et al., Nat Med, 2004, 10, (1), 33-39;Visakorpi T et al., Nat Genet, 1995, 9, (4), 401-406). Recent studiesdemonstrated that BRD4 inhibition can disrupt AR recruitment to targetgene loci and exhibits much more effective mCRPC treat-ment than directAR antagonism (i.e., enzalutamide) (Asangani, I A. et al., Nature 2014,510, (7504), 278-282).

Motivated by the important role of BRD4 to regulate AR signaling pathwayand PCa progression, BRD4 siRNA was encapsulated in the multi-staged NPplatform. It was evaluated whether this multi-staged siRNA deliveryplatform can silence the BRD4 expression in vivo and show anticancereffect. To assess the in vivo BRD4 silencing, the BRD4 siRNA loaded NPswere intravenously injected into the LNCaP xenograft tumor-bearing mice(1 nmol siRNA dose per mouse, n=3) for three consecutive days. Westernblot analysis of the tumor tissue showed that the administration of BRD4siRNA loaded NPs leads to around 85% knockdown in BRD4 expressioncompared to the control NPs loaded with Luc siRNA. A similar tendencywas also observed in the immunohistochemistry (IHC) staining analysis.With this suppressed BRD4 expression, there is a significant increase intumor cell apoptosis confirmed by TUNEL staining. Additionally, theadministration of the TCPA2-NPs shows negligible in vivo side effects.After three consecutive injections of the NPs to healthy mice (onceevery two days at a 1 nmol siRNA dose per mouse, n=3), there were nonoticeable histological changes in the tissues from heart, liver,spleen, lung or kidney. Blood serum analysis shows that TNF-α, IFN-γ,IL-6, and IL-12 levels are in the normal range 24 hour post injection.To confirm whether the NP-mediated BRD4 silencing has an anti-cancereffect, the BRD4 siRNA loaded NPs were intravenously injected into theLNCaP xenograft tumor-bearing mice once every three days at a 1 nmolsiRNA dose per mouse (n=5). After four consecutive injections, the tumorgrowth is significantly inhibited compared to the mice treated with PBS,naked BRD4 siRNA or Luc siRNA loaded NPs (FIGS. 44A-45B). There is lessthan 1.5-fold increase (from ˜63 to ˜81 mm3) in tumor size of the micetreated with the BRD4 siRNA loaded NPs at day 16 (FIG. 44A). However,for the mice treated with other formulations, their tumor size (FIG.44A) and weight (FIG. 44B) are more than 4-fold larger than that of micetreated with the BRD4 siRNA loaded NPs. In addition, similar as thehistological analysis results, the BRD4 siRNA loaded NPs shows noobvious influence on mouse body weight, implying good biocompatibilityof this NP platform. The results show that the systemic delivery of BRD4siRNA can efficiently silence BRD4 expression in the tumor tissue andsignificantly inhibit PCa tumor growth with negligible toxicities.

Thus, a TME pH-responsive multi-staged NP platform for systemic siRNAdelivery and effective cancer therapy has successfully developed. Invitro and in vivo results show that this multi-staged NP platform canfirst highly accumulate at tumor site via long blood circulation andthen respond to TME pH to fast expose siRNA/TCPA complex, whichsubsequently target and penetrate to induce strong cytosolic siRNAdelivery and efficient in vivo gene silencing.

1. Stimuli responsive amphiphilic polymers which self-assemble to formnanoparticles, wherein the stimuli are selected from the groupconsisting of pH, temperature, light, redox change, over-expressedenzymes, hypoxia, sound, magnetic force, electrical energy, andcombinations thereof.
 2. The polymers of claim 1 wherein the hydrophobicportion of the amphiphilic polymers changes shape and/or degrades uponexposure to the stimuli.
 3. The polymers of claim 1 wherein the polymersresponsive to pH are selected from the group consisting of poly(2-(diisopropylamino) ethylmethacrylate (PDPA),poly(2-(hexamethyleneimino) ethyl methacrylate (PHMEMA), conjugates andderives thereof thereof.
 4. The polymers of claim 3 wherein the polymerderivatives are selected from the group consisting ofmethoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate) (Meo-PEG-b-PDPA), methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidyl methacrylate)(Meo-PEG-b-P(DPA-co-GMA)), methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidylmethacrylate-tetraethylenepentamine) (Meo-PEG-b-P(DPA-co-GMA-TEPA)),methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate-tetraethylenepentamine-C14)(Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)), methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidylmethacrylate-oligoarginine) (Meo-PEG-b-P(DPA-co-GMA-Rn)),methoxyl-polyethylene glycol-b-poly(2-(hexamethyleneimino) ethylmethacrylate) (Meo-PEG-b-PHMEMA), and poly (2-(hexamethyleneimino) ethylmethacrylate-co-2-aminoethyl methacrylate) Meo-PEG-b-P(HMEMA-co-AMA). 5.The polymers of claim 1 which are responsive to light selected from thegroup consisting of methoxyl-polyethylene glycol-b-poly(2-(2-oxo-2-phenylacetoxy) ethyl methacrylate) (Meo-PEG-b-POPEMA) andmixtures thereof.
 6. The polymers of claim 1 which are redox responsiveselected from the group consisting of L-cystine-based poly(disulfide)(PDSA) polymers.
 7. Nanoparticles formed by emulsion with a non-aqueoussolvent, solvent extraction, or nanoprecipitation from polymers incombination with stimuli responsive polymers, wherein the stimuli areselected from the group consisting of pH, temperature, light, redoxchange, over-expressed enzymes, hypoxia, sound, magnetic force,electrical energy, and combinations thereof.
 8. The nanoparticles ofclaim 7 wherein the polymers comprise a first amphiphilic polymercontaining a polymer represented by Formula I:(X)_(m)—(Y)_(n)   Formula I wherein m and n are independently integersbetween one and 1000, inclusive, X is a hydrophobic polymer and Y is ahydrophilic polymer, and at least one of X, Y, or both, isstimuli-responsive.
 9. The nanoparticles of claim 8 comprising a mixtureof polymers represented by Formula I and a second polymer containing apolymer represented by Formula II:(Q)_(c)-(R)_(d)   Formula II Wherein c and d are independently integersbetween zero and 1000, inclusive, with the proviso that the sum (c+d) isgreater than one, and Q and R are independently hydrophilic orhydrophobic polymers.
 10. The nanoparticles of claim 7 wherein thepolymer represented by Formula I, Formula II, or both, contains aligand.
 11. The nanoparticles of claim 10, wherein the ligand is atargeting ligand, an adhesion ligand, a cell-penetrating ligand, or anendosomal-penetrating ligand.
 12. The nanoparticles of claim 10, whereinthe ligand is selected from the group consisting of a disulfide-basedcyclic arginine-glycine-aspartic acid (RGD) peptide (iRGD), a tumortargeting moiety S,S-2-[3-[5-amino-1-carboxypentyl]-ureido]-pentanedioicacid (ACUPA), and oligoarginine, and combinations thereof.
 13. Thenanoparticles of claim 7 further comprising a stimuli-responsivehydrophobic polymer
 14. The nanoparticles of claim 7 wherein thehydrophilic portion of the amphiphilic polymers is a polyalkylene oxide,or derivative thereof.
 15. The nanoparticles of claim 7 wherein thepolymers comprising polymer responsive to pH selected from the groupconsisting of poly (2-(diisopropylamino) ethylmethacrylate (PDPA),poly(2-(hexamethyleneimino) ethyl methacrylate (PHMEMA), conjugates andderives thereof thereof, conjugates and derives thereof.
 16. Thenanoparticles of claim 5 wherein the polymers comprising polymerresponsive to pH selected from the group consisting ofmethoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate) (Meo-PEG-b-PDPA), methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidyl methacrylate)(Meo-PEG-b-P(DPA-co-GMA)), methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidylmethacrylate-tetraethylenepentamine) (Meo-PEG-b-P(DPA-co-GMA-TEPA)),methoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate-tetraethylenepentamine-C14)(Meo-PEG-b-P(DPA-co-GMA-TEPA-C14)), methoxyl-polyethylene glycol-b-poly(2-(diisopropylamino) ethylmethacrylate-co-glycidylmethacrylate-oligoarginine) (Meo-PEG-b-P(DPA-co-GMA-Rn)),methoxyl-polyethylene glycol-b-poly(2-(hexamethyleneimino) ethylmethacrylate) (Meo-PEG-b-PHMEMA), and poly (2-(hexamethyleneimino) ethylmethacrylate-co-2-aminoethyl methacrylate) Meo-PEG-b-P(HMEMA-co-AMA),conjugates and derives thereof.
 17. The nanoparticles of claim 7comprising therapeutic, prophylactic, or diagnostic agents selected fromthe group consisting of proteins or peptides, nucleic acids, lipids,sugars or polysaccharides, small molecules, or combinations thereof. 18.The nanoparticles of claim 17 comprising between about 1% and about 70%weight/weight, between about 5% and about 50% weight/weight, or betweenabout 10% and about 30% weight/weight of a therapeutic agent, aprophylactic agent, a diagnostic agent, or combinations thereof.
 19. Thenanoparticles of claim 17 release agent primarily within target certaincells, tissues or organs of the body, upon exposure to endogenous orexogenous stimuli.
 20. The nanoparticles of claim 17 where the agent isreleased as a burst, sustained, delayed, or a combination thereof. 21.The nanoparticles of claim 17 wherein the agent is small interferenceRNA (siRNA), RNA interference (RNAi), miRNA, or other regulatory nucleicacid molecules.
 22. The nanoparticles of claim 17 wherein the agent is achemotherapeutic, or antiinfective for treatment of a disordercharacterized by a stimuli effecting release or which can be exposed toa stimuli.
 23. The nanoparticles of claim 22 releasing achemotherapeutic, or antiinfective at a site of low pH caused by canceror an infection.
 24. The nanoparticles of claim 7 wherein the polymerscomprise polymer selected from the group consisting ofmethoxyl-polyethylene glycol-b-poly (2-(diisopropylamino)ethylmethacrylate-co-glycidyl methacrylate)(Meo-PEG-b-P(DPA-co-GMA-TEPA-C14), Meo-PEG-b-P(DPA-co-GMA-TEPA-Cy5.5),iRGD-PEG-b-PDPA, and mixtures thereof.
 25. The nanoparticles of claim 7wherein membrane-penetrating oligoarginine grafts, and/or anS,S-2-[3-[5-amino-1-carboxypentyl]-ureido]-pentanedioic acid (ACUPA)terminus are bound to the polymer.
 26. The nanoparticles of claim 5comprising a mixture of Meo-PEG-b-P(DPA-co-GMA-Rn), andACUPA-PEG-b-PDPA.
 27. The nanoparticles of claim 26 comprising a mixtureof Meo-PEG-b-P(DPA-co-GMA-Rn) (90 mol %) and ACUPA-PEG-b-PDPA (10 mol%).
 28. The nanoparticles of claim 7 wherein the stimulus is pH.
 29. Thenanoparticles of claim 7 wherein the stimulus is temperature.
 30. Thenanoparticles of claim 7 wherein the stimuli is a change in redox,light, sound, oxygen concentration, or electrical energy.
 31. A methodof making the nanoparticles of claim 7 comprising adding polymer andoptionally agent to an emulsion of an aqueous and a non-aqueous solventto form stimuli responsive nanoparticles.
 32. A method of deliveringtherapeutic, prophylactic, and/or diagnostic agents comprisingadministering the nanoparticles of claim 17 and exposing thenanoparticles thereafter to the stimulus causing release of agent to bedelivered.